System and method for segmenting a cardiac signal based on brain stimulation

ABSTRACT

A medical device system that includes a brain stimulating element, cardiac monitoring element and a processor. The processor is configured to receive a brain stimulation signal from the brain stimulating element and a cardiac signal from the cardiac monitoring element. The processor is further configured to determine at least one reference point for a stimulation event time period by evaluation of the brain stimulation signal. The processor further identifies a first portion of the cardiac signal based on the at least one reference point of the stimulation event time period.

RELATED APPLICATION

This application is a continuation-in-part of U.S. application Ser. No. 11/380,462, filed Apr. 27, 2006; a continuation-in-part of U.S. application Ser. No. 11/311,043, filed Dec. 19, 2005; a continuation-in-part of U.S. application Ser. No. 11/311,200, filed Dec. 19, 2005; a continuation-in-part of U.S. application Ser. No. 11/311,393, filed Dec. 19, 2005; a continuation-in-part of U.S. application Ser. No. 11,311,456, filed Dec. 19, 2005, each of which claim the benefit of U.S. Provisional Application Ser. No. 60/636,929, filed Dec. 17, 2004, and all of which are incorporated herein by reference.

FIELD OF THE INVENTION

This invention relates generally to medical devices, systems and methods, and more particularly to the monitoring of cardiac signals associated with neurological events.

BACKGROUND OF THE INVENTION

Nervous system disorders affect millions of people, causing death and a degradation of life. Nervous system disorders include disorders of the central nervous system, peripheral nervous system, and mental health and psychiatric disorders. Such disorders include, for example without limitation, epilepsy, Parkinson's disease, essential tremor, dystonia, and multiple sclerosis (MS). Additionally, nervous system disorders include mental health disorders and psychiatric disorders which also affect millions of individuals and include, but are not limited to, anxiety (such as general anxiety disorder, panic disorder, phobias, post traumatic stress disorder (PTSD), and obsessive compulsive disorder (OCD)), mood disorders (such as major depression, bipolar depression, and dysthymic disorder), sleep disorders (narcolepsy), eating disorders such as obesity, and anorexia. As an example, epilepsy is the most prevalent serious neurological disease across all ages. Epilepsy is a group of neurological conditions in which a person has or is predisposed to recurrent seizures. A seizure is a clinical manifestation resulting from excessive, hypersynchronous, abnormal electrical or neuronal activity in the brain. A neurological event is an activity that is indicative of a nervous system disorder. A seizure is a type of a neurological event. This electrical excitability of the brain may be likened to an intermittent electrical overload that manifests with sudden, recurrent, and transient changes of mental function, sensations, perceptions, or involuntary body movement.

Because the seizures are unpredictable, epilepsy affects a person's employability, psychosocial life, and ability to operate vehicles or power equipment. It is a disorder that occurs in all age groups, socioeconomic classes, cultures, and countries.

There are various approaches to treating nervous system disorders. Treatment therapies can include any number of possible modalities alone or in combination including, for example, electrical stimulation, magnetic stimulation, drug infusion, or brain temperature control. Each of these treatment modalities may use open loop treatment where neither the timing of the therapy nor treatment parameters are automatically set or revised based on information coming from a sensed signal. Each of these treatment modalities may also be operated using closed-loop feedback control. Such closed-loop feedback control techniques may receive from a monitoring element a brain signal (such as EEG, ECoG, intracranial pressure, change in quantity of neurotransmitters) that carries information about a symptom or a condition of a nervous system disorder and is obtained from the head or brain of the patient.

For example, U.S. Pat. No. 5,995,868 discloses a system for the prediction, rapid detection, warning, prevention, or control of changes in activity states in the brain of a patient. Use of such a closed-loop feed back system for treatment of a nervous system disorder may provide significant advantages in that treatment can be delivered before the onset of the symptoms of the nervous system disorder.

While much work has been done in the area of detecting nervous system disorders by processing EEG signals, less has been done in the area of the brain-heart relationship as it pertains to these disorders. The relationship between the heart and the brain is complex and not fully understood. While some references discuss monitoring cardiac and brain activity, the question of what the device or system should do once it receives those signals has not been fully explored.

Sudden unexpected death in epilepsy, or SUDEP, is just one example of a nervous system disorder that involves a relationship between the brain and the heart. SUDEP, is defined as sudden, unexpected, often unwitnessed, non-traumatic and non-drowning death in patients for which no cause has been found except for the individual having a history of seizures. Depending on the cohort studied, SUDEP is responsible for 2% to 18% of all deaths in patients with epilepsy, and the incidence may be up to 40 times higher in young adults with epilepsy than among persons without seizures. Although the pathophysiological mechanisms leading to death are not fully understood, experimental, autopsy and clinical evidence implicate seizure related heart and pulmonary dysfunction or indicators. Pulmonary events may include obstructive sleep apnea (OSA), central apnea, and neurogenic pulmonary edema. Cardiac events may include cardiac arrhythmic abnormalities including sinus arrhythmia, sinus pause, premature atrial contraction (PAC), premature ventricular contraction (PVC), irregular rhythm (wandering pacemaker, multifocal atrial tachycardia, atrial fibrillation), asystole or paroxysmal tachycardia. Cardiac events may also include conduction abnormalities including AV-block (AVB) and bundle branch block (BBB), and repolarization abnormalities including T-wave inversion and ST-elevation or depression. Lastly, hypertension, hypotension and vaso-vagal syncope (VVS) are common in epilepsy patients.

Epileptic seizures are associated with autonomic neuronal dysfunction that results in a broad array of abnormalities of cardiac and pulmonary function. Different pathophysiological events may contribute to SUDEP in different patients, and the mechanism is probably multifactorial. Without intervention, respiratory events, including airway obstruction, central apnea and neurogenic pulmonary edema are probably terminal events. In addition, cardiac arrhythmia and anomalies, during the stimulation and interstimulation periods, leading to arrest and acute cardiac failure also plays an important role in potentially terminal events. For example, the paper “Electrocardiographic Changes at Seizure Onset”, Leutmezer, et al, Epilepsia 44(3): 348-354, 2003 describes cardiovascular anomalies, such as heart rate variability (HRV), tachycardia and bradycardia, that may precede, occur simultaneous or lag behind EEG seizure onset. “Cardiac Asystole in Epilepsy: Clinical and Neurophysiologic Features”, Rocamora, et al, Epilepsia 44(2): 179-185, 2003 reports that cardiac asystole is “provoked” by the seizure. “Electrocardiograph QT Lengthening Associated with Epileptiform EEG Discharges—a Role in Sudden Unexplained Death in Epilepsy”, Tavemor, et al, Seizure 5(1): 79-83, March 1996 reports QT lengthening during seizures in SUDEP patients versus control. “Effects of Seizures on Autonomic and Cardiovascular Function”, Devinsky Epilepsy Currents 4(2): 43-46, March/April 2004 describes ST segment depression and T-wave inversion, AVB, VPC and BBB during or immediately after a seizure. “Sudden Unexplained Death in Children with Epilepsy”, Donner, et al, Neurology 57: 430-434, 2001 reports that bradycardia is frequently preceded by hypoventilation or apnea suggesting that heart rate changes during seizures may be a result of cardiorespiratory reflexes. Lastly, “EEG and ECG in Sudden Unexplained Death in Epilepsy”, Nei, et al, Epilepsia 45(4) 338-345, 2004 reports on sinus tachycardia during or after seizures.

With the above broad and, often conflicting, array of neuro-cardiopulmonary physiological anomalies, manifestations and indicators, a device, or array of devices, is desired to allow for better diagnosis, monitoring and/or treatment of nervous system disorders including monitoring of both cardiac and brain signals.

SUMMARY OF THE INVENTION

In one embodiment of the invention, a medical device system is provided that includes a brain stimulating element, cardiac monitoring element and a processor. The processor is configured to receive a brain stimulation signal from the brain stimulating element and a cardiac signal from the cardiac monitoring element. The processor is further configured to determine at least one reference point for a brain stimulation event time period by evaluation of the brain stimulation signal. The processor identifies a first portion of the cardiac signal based on the at least one reference point of the brain stimulation event time period. Many additional embodiments are disclosed relating to the segmentation of the cardiac signal based on evaluation of the brain stimulation signal and in some embodiments including evaluation of the cardiac signal.

BRIEF DESCRIPTION OF THE DRAWINGS

Core Monitor

FIG. 1 is a simplified schematic view of a thoracic cavity leadless medical device implanted in a patient that monitors cardiac and respiratory parameters relating to a nervous system disorder.

FIG. 2 is a simplified schematic view of an alternative embodiment cardiac leaded medical device implanted in a patient that monitors cardiac and respiratory parameters relating to nervous system disorder.

FIG. 3 is a simplified schematic view of an alternative embodiment sensor stub medical device implanted in a patient that monitors cardiac and respiratory parameters relating to nervous system disorder.

FIG. 4 is a simplified schematic view of an alternative embodiment external patch medical device used by a patient that monitors cardiac and respiratory parameters relating to nervous system disorder.

Full Monitor

FIG. 5 is a simplified schematic view of an alternative embodiment thoracic leadless and cranial leaded medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorder.

FIG. 6 is a simplified schematic view of an alternative embodiment cardiac and cranial leaded medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorder.

FIG. 7 is a simplified schematic view of an alternative embodiment sensor stub and cranial leaded medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorder.

FIG. 8 is a simplified schematic view of an alternative embodiment external patch and cranial leaded medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorder.

FIG. 9 is a simplified schematic view of an alternative embodiment integrated brain lead medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorder.

FIG. 10 is a simplified schematic view of an alternative embodiment cranial implant medical device implanted in a patient that monitors cardiac and brain parameters relating to nervous system disorder.

Monitor+Treatment (Brain)

FIG. 11 is a simplified schematic view of an alternative embodiment thoracic leadless and cranial leaded medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorders and provides brain treatment.

12A is a simplified schematic view of an alternative embodiment cardiac and cranial leaded medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorders and provides brain treatment.

FIG. 12B is a simplified schematic view of an alternative embodiment cardiac and cranial leaded medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorders and provides brain treatment.

FIG. 13 is a simplified schematic view of an alternative embodiment sensor stub and cranial leaded medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorders and provides brain treatment.

FIG. 14 is a simplified schematic view of an alternative embodiment external patch and cranial leaded medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorders and provides brain treatment.

FIG. 15 is a simplified schematic view of an alternative embodiment integrated brain lead medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorders and provides brain treatment.

FIG. 20 is a simplified schematic view of an alternative embodiment thoracic leadless device to cranial implant via wireless connect medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorders and provides brain treatment.

FIG. 21 is a simplified schematic view of an alternative embodiment external patch to cranial implant via wireless connect medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorders and provides brain treatment.

Monitor+Treatment (Brain+Respiration)

FIG. 16A is a simplified schematic view of an alternative embodiment cardiac, brain and phrenic nerve leaded medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorders and provides brain and respiration treatment.

FIG. 16B is a simplified schematic view of an alternative embodiment cardiac, brain and phrenic nerve leaded medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorders and provides brain and respiration treatment.

FIG. 17 is a simplified schematic view of an alternative embodiment sensor stub, brain and phrenic nerve leaded medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorders and provides brain and respiration treatment.

FIG. 18 is a simplified schematic view of an alternative embodiment integrated brain and phrenic nerve leaded medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorders and provides brain and respiration treatment.

FIG. 19 is a simplified schematic view of an alternative embodiment brain and integrated respiration lead medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorders and provides brain and respiration treatment.

Monitor+Treatment (Brain+Cardiac)

FIG. 24A is a simplified schematic view of an alternative embodiment cardiac and brain leaded medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorders and provides brain and cardiac treatment.

FIG. 24B is a simplified schematic view of an alternative embodiment cardiac and brain leaded medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorders and provides brain and cardiac treatment.

FIG. 22 is a simplified schematic view of an alternative embodiment cranial implant to defibrillator vest via wireless connect medical device used by a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorders and provides brain and cardiac treatment.

FIG. 23 is a simplified schematic view of an alternative embodiment cranial implant to leadless defibrillator (lifeboat) via wireless connect medical device used by a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorders and provides brain and cardiac treatment.

Monitor+Treatment (Brain+Respiration+Cardiac)

FIG. 25A is a simplified schematic view of an alternative embodiment cardiac, cranial and phrenic nerve leaded medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorders and provides brain and respiration and cardiac treatment.

FIG. 25B is a simplified schematic view of an alternative embodiment cardiac, cranial and phrenic nerve leaded medical device implanted in a patient that monitors cardiac, respiratory and brain parameters relating to nervous system disorder and provides brain and respiration and cardiac treatment.

Detailed Design

FIG. 26 is a simplified block diagram of a core monitor as shown in FIG. 1 above.

FIG. 27 is a graphical representation of the signals sensed by core monitor as shown in FIG. 1 above.

FIG. 28 is a simplified block diagram of a core monitor as shown in FIG. 2 above.

FIG. 29 is a simplified block diagram of a core monitor as shown in FIG. 3 above.

FIG. 30 is a simplified block diagram of a core monitor as shown in FIG. 4 above.

FIG. 31 is a flow diagram showing operation of a core monitor as shown in FIGS. 1-4 above.

FIG. 32 is a simplified block diagram of a full monitor as shown in FIG. 5 above.

FIG. 33 is a simplified block diagram of a full monitor as shown in FIG. 6 above.

FIG. 34 is a simplified block diagram of a full monitor as shown in FIG. 7 and 9 above.

FIG. 35 is a simplified block diagram of a full monitor as shown in FIG. 8 above.

FIG. 36 is a simplified block diagram of a full monitor as shown in FIG. 10 above.

FIG. 37 is a flow diagram showing operation of a full monitor as shown in FIGS. 5-10 above.

FIG. 38 is a diagram of exemplary physiologic data from a patient with a full monitor as shown in relation to FIGS. 5-10 above.

FIG. 39 shows a process for identifying ECG and respiratory abnormalities recorded during detected seizures in a full monitor as shown in relation to FIGS. 5-10 above.

FIG. 40A shows a process for enabling the cardiac or respiratory detectors for neurological event detection in a full monitor as shown in relation to FIGS. 5-10 above and detection/treatment as described in FIGS. 41-51 below.

FIG. 40B shows a process for enabling the ECG or respiratory detectors for seizure detection in a full monitor as shown in relation to FIGS. 5-10 above and detection/treatment as described in FIGS. 41-51 below.

FIG. 41 is a simplified block diagram of a full monitor with brain stimulation therapy as shown in FIG. 11 above.

FIG. 42 is a simplified block diagram of a full monitor with brain stimulation therapy as shown in FIG. 12A above.

FIG. 43 is a simplified block diagram of a full monitor with brain stimulation therapy as shown in FIG. 12B above.

FIG. 44 is a simplified block diagram of a full monitor with brain stimulation therapy as shown in FIGS. 13 and 15 above.

FIG. 45 is a simplified block diagram of a full monitor with brain stimulation therapy as shown in FIG. 14 above.

FIG. 46 is a simplified block diagram of a full monitor with brain stimulation therapy as shown in FIG. 20 above.

FIG. 47 is a simplified block diagram of a full monitor with brain stimulation therapy as shown in FIG. 21 above.

FIG. 48 is a simplified block diagram of a full monitor with brain and respiration stimulation therapy as shown in FIG. 16A above.

FIG. 49 is a simplified block diagram of a full monitor with brain and respiration stimulation therapy as shown in FIG. 16B above.

FIG. 50 is a simplified block diagram of a full monitor with brain and respiration stimulation therapy as shown in FIGS. 17, 18 and 19 above.

FIG. 51 is a simplified block diagram of a full monitor with brain and cardiac stimulation therapy as shown in FIG. 24A above.

FIG. 52 is a simplified block diagram of a full monitor with brain and cardiac stimulation therapy as shown in FIG. 24B above.

FIG. 53 is a simplified block diagram of a full monitor with brain and cardiac stimulation therapy as shown in FIGS. 22 and 23 above.

FIG. 54 is a simplified block diagram of a full monitor with brain, respiration and cardiac stimulation therapy as shown in FIG. 25A above.

FIG. 55 is a simplified block diagram of a full monitor with brain, respiration and cardiac stimulation therapy as shown in FIG. 25B above.

FIG. 56 is a flow diagram showing operation of a full monitor with therapy (including brain, respiration or cardiac stimulation therapy) as shown in FIGS. 11-25 above.

FIG. 57A is a flow diagram showing a process for enabling cardiac/respiratory detectors for neurological event detection and treatment including termination rules.

FIG. 57B is a flow diagram showing a process for enabling ECG/respiratory detectors for seizure detection and treatment including termination rules.

FIG. 58 is a schematic diagram of a system utilizing any of the above-described embodiments and allowing remote monitoring and diagnostic evaluation of at risk patients.

FIG. 59 is a schematic diagram of an alternative system utilizing any of the above-described embodiments and allowing remote monitoring and diagnostic evaluation of at risk patients.

FIG. 60 is a flowchart illustrating one embodiment method of identifying a portion of a cardiac signal based on a reference point in a brain signal.

FIG. 61 is a flowchart illustrating a more detailed embodiment method of identifying a portion of a cardiac signal based on starting and ending points of a neurological event in a brain signal.

FIG. 62 is a chart of EEG and ECG signals showing exemplary relationships between the two signals.

FIG. 63 is another chart of EEG and ECG signals showing exemplary relationships between the two signals.

FIG. 64 is a flowchart illustrating one embodiment method of identifying a portion of a cardiac signal based on a reference point in a brain stimulation signal.

FIG. 65 is a flowchart illustrating a more detailed embodiment method of identifying a portion of a cardiac signal based on starting and ending points of a brain stimulation signal.

FIG. 66 is a chart of EEG and ECG signals showing exemplary relationships between the two signals.

FIG. 67 is another chart of EEG and ECG signals showing exemplary relationships between the two signals.

FIG. 68 shows one embodiment process for identifying ECG and respiratory abnormalities recorded during delivered stimulations.

DETAILED DESCRIPTION OF THE INVENTION

The term “brain monitoring element” used herein means any device, component or sensor that receives a physiologic signal from the brain or head of a patient and outputs a brain signal that is based upon the sensed physiologic signal. Some examples of a brain monitoring element include leads, electrodes, chemical sensors, biological sensors, pressure sensors, and temperature sensors. A monitoring element does not have to be located in the brain to be a brain monitoring element. The term brain monitoring element is not the same as the term “monitor” also used herein, although a brain monitoring element could be a part of a monitor.

The term “cardiac monitoring element” used herein means any device, component or sensor that receives or infers a physiological signal from the heart of a patient and outputs a cardiac signal that is based upon sensed physiologic signal. Some examples of cardiac monitoring elements include leads, electrodes, chemical sensors, biological sensor, pressure sensors and temperature sensors. A monitoring element does not have to be located in the heart or adjacent to the heart to be a cardiac monitoring element. For example, a sensor or electrode adapted for sensing a cardiac signal and placed on the housing of an implantable device is a cardiac monitoring element. Furthermore, a cardiac monitoring element could be an externally placed sensor such as a holter monitoring system. The term “cardiac monitoring element” is not the same as the term “monitor” also used herein although a cardiac monitoring element could be a part of a monitor.

The term “respiratory monitoring element” used herein means any device, component or sensor that receives a physiologic signal indicative of activity or conditions in the lungs of a patient and outputs a respiration signal that is based upon the sensed physiologic signal. Some examples of respiration monitoring elements are provided below. A monitoring element does not have to be located in the lungs or adjacent to the lungs to be a respiratory monitoring element. The term “respiratory monitoring element” is not the same as the term “monitor” also used herein although a respiratory monitoring element could be a part of a monitor.

It is noted that many embodiments of the invention may reside on any hardware embodiment currently understood or conceived in the future. Many example hardware embodiments are provided in this specification. These examples are not meant to be limiting of the invention.

Core Monitor

Cardiopulmonary monitoring in the Core Monitor device (as described below in more detail in conjunction with FIGS. 1-4 and 26-30) monitors cardiac (e.g., ECG, blood pressure) or respiration signals continuously and records these signals in a loop recorder either automatically or manually when the patient indicates they have had a neurological event such as a seizure. Real-time analysis of the ECG signal evaluates rate disturbances (e.g., bradycardia; tachycardia; asystole) as well as any indications of cardiac ischemia (e.g., ST segment changes; T wave inversion, etc.). Real-time analysis of the respiration signal evaluates respiration disturbances (e.g., respiration rate, minute ventilation, apnea, prolonged pauses).

Abnormalities detected during real-time analysis will lead to an immediate patient alert. This alert can be audible (beeps, buzzers, tones, spoken voice, etc.), light, tactile, or other means.

Automatic loop recording may save the data for a programmable period of time. For example, the device may be programmed to save a period of time before a cardiac detection (e.g., 30 seconds of ECG raw or processed data before detection) and a second period of time after the detection (e.g., 3 minutes of ECG raw or processed data after detection).

The medical device system may also include a manual activation mode in which the patient provides an indication (e.g., push a button on a holter, patient programmer or other external patient activator device) when a neurological event is occurring or has just occurred. In manual activation mode, to allow for the fact that the patient may not mark the neurological event until the neurological event has ended, the ECG loop recording may begin a longer time period before the event is marked. For example, the medical device system may save ECG data beginning 15 minutes before the patient mark. This time period may be programmable. Post-processing of this saved signal will analyze the data to evaluate heart rate changes during the neurological event, heart rate variability and changes in ECG waveforms. Manual patient indication of a neurological event will be done through the patient external activator device 22. The patient (or caregiver) will push a button on the external device, while communicating with the implanted device. This will provide a marker and will initiate a loop recording. In addition, prolonged ECG loop recordings are possible (e.g., in the case of SUDEP, recording all data during sleep since the incidence of SUDEP is highest in patients during sleep).

Post-processing of the signal can occur in the implanted device, the patient's external device or in the clinician external device. Intermittently (e.g., every morning, once/week, following a neurological event), the patient may download data from the implantable device to the patient external device. This data will then be analyzed by the external device (or sent through a network to the physician) to assess any ECG or respiratory abnormalities. If an abnormality is detected, the device will notify the patient/caregiver. At that time, the patient/caregiver or device can inform the healthcare provider of the alert to allow a full assessment of the abnormality. The clinician external device is also capable of obtaining the data from the implanted device and conducting an analysis of the stored signals. If a potentially life-threatening abnormality is detected, the appropriate medical treatment can be prescribed (e.g., cardiac abnormality: a pacemaker, an implantable defibrillator, or a heart resynchronization device may be indicated or respiration abnormality: CPAP, patient positioning, or stimulation of respiration may be indicated).

FIG. 1 is a simplified schematic view of one embodiment of a core Monitor 100 implanted in a patient 10. Monitor 100 continuously senses and monitors the cardiac and respiration function of patient 10 via one or more monitoring elements 14 (e.g., cardiac electrodes) to allow detection of neurological events, the recording of data and signals pre and post event. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data.

Monitor 100, as stated above, typically includes one or more monitoring elements 14 such as several subcutaneous spiral electrodes that are embedded individually into three or four recessed casings placed in a compliant surround that is attached to the perimeter of implanted monitor 100 as substantially described in U.S. Pat. No. 6,512,940 “Subcutaneous Spiral Electrode for Sensing Electrical Signals of the Heart” to Brabec, et al and U.S. Pat. No. 6,522,915 “Surround Shroud Connector and Electrode Housings for a Subcutaneous Electrode Array and Leadless ECGS” to Ceballos, et al. These electrodes are electrically connected to the circuitry of the implanted Monitor 100 to allow the detection of cardiac depolarization waveforms (as substantially described in U.S. Pat. No. 6,505,067 “System and Method for Deriving a Virtual ECG or EGM Signal” to Lee, et al.) that may be further processed to detect cardiac electrical characteristics (e.g., heart rate, heart rate variability, arrhythmias, cardiac arrest, sinus arrest and sinus tachycardia). Further processing of the cardiac signal amplitudes may be used to detect respiration characteristics (e.g., respiration rate, minute ventilation, and apnea).

To aid in the implantation of Monitor 100 in a proper position and orientation, an implant aid may be used to allow the implanting physician to determine the proper location/orientation as substantially described in U.S. Pat. No. 6,496,715 “System and Method for Noninvasive Determination of Optimal Orientation of an Implantable Sensing Device” to Lee, et al.

FIG. 2 is a simplified schematic view of a second embodiment core Monitor 120 implanted in a patient 10. Monitor 120 continuously senses and monitors cardiac and respiration function of patient 10 via cardiac lead(s) 16 to allow detection of neurological events and the recording of data and signals pre and post event. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data. Monitor 120 senses both cardiac signals and respiration parameters via standard cardiac leads implanted in the heart. Monitor 120 measures intra-cardiac impedance, varying both with the intrathoracic pressure fluctuations during respiration and with cardiac contraction is representative of the pulmonary activity and of the cardiac activity as substantially described in U.S. Pat. No. 5,003,976 “Cardiac and Pulmonary Physiological Analysis via Intracardiac Measurements with a Single Sensor” to Alt. Cardiac leads 16 may consist of any typical lead configuration as is known in the art, such as, without limitation, right ventricular (RV) pacing or defibrillation leads, right atrial (RA) pacing or defibrillation leads, single pass RA/RV pacing or defibrillation leads, coronary sinus (CS) pacing or defibrillation leads, left ventricular pacing or defibrillation leads, pacing or defibrillation epicardial leads, subcutaneous defibrillation leads, unipolar or bipolar lead configurations, or any combinations of the above lead systems.

FIG. 3 is a simplified schematic view of a third embodiment core Monitor 140 implanted in a patient 10. Monitor 140 continuously senses and monitors cardiac and respiration function of patient 10 via an electrode (not shown) located distally on sensor stub 20 which is inserted subcutaneously in the thoracic area of the patient to allow detection of neurological events and the recording of data and signals pre and post event. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data. Monitor 140 senses cardiac signals between an electrode on the distal end of the sensor stub and the monitor case as described in conjunction with the embodiment shown in FIG. 5 in U.S. Pat. No. 5,987,352 “Minimally Invasive Implantable Device for Monitoring Physiologic Events” to Klein, et al. Monitor 140 also senses respiration parameters such as respiration rate, minute ventilation and apnea via measuring and analyzing the impedance variations measured from the implanted monitor 140 case to the electrode (not shown) located distally on sensor stub lead 20 as substantially described in U.S. Pat. No. 4,567,892 “Implantable Cardiac Pacemaker” and U.S. Pat. No. 4,596,251 “Minute Ventilation Dependent Rate Responsive Pacer” both to Plicchi, et al.

FIG. 4 is a simplified schematic view of a fourth embodiment core Monitor 160 attached to a patient 10. External patch Monitor 160 continuously senses and monitors cardiac and respiration function of patient 10 to allow detection of neurological events and the recording of data and signals pre and post event. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data. Also optionally, a button 38 on the external patch monitor 160 may be activated by the patient 10 to manually activate diagnostic data recording.

External patch Monitor 160 consists of a resilient substrate affixed to the patient's skin with the use of an adhesive which provides support for an amplifier, memory, microprocessor, receiver, transmitter and other electronic components as substantially described in U.S. Pat. No. 6,200,265 “Peripheral Memory Patch and Access Method for Use With an Implantable Medical Device” to Walsh, et al. The substrate flexes in a complimentary manner in response to a patient's body movements providing patient comfort and wearability. The low profile external patch Monitor 160 is preferably similar in size and shape to a standard bandage, and may be attached to the patient's skin in an inconspicuous location. Uplinking of stored physiologic telemetry data from the internal memory of external patch Monitor 160 may be employed to transfer information between the monitor and programmer 12.

Full Monitor

The term “full monitor” is used to describe a monitor that is capable of monitoring the brain (such as by monitoring a brain signal such as an electroencephalogram (EEG)) and additionally the heart or pulmonary system or both. This will allow the full monitor to collect neurological signals and at least one of the cardiovascular and respiratory signals in close proximity to neurological events detected (such as seizures) as well as notifying the patient/caregiver of a prolonged neurological event (such as status epilepticus). Cardiovascular and respiratory monitoring may occur around a neurological event (in the case of a seizure this is called peri-stimulation). In distinction from the core monitor, in which patients/caregivers must notify the device that a neurological event has occurred, the full monitor device will detect the neurological event (based on the brain signal) and will automatically analyze the peri-stimulation signals and initiate the loop recording. Monitoring of more than one physiologic signal allows for greater understanding of the total physiologic condition of the patient. For example, prolonged or generalized seizures put patients at higher risk for SUDEP, the EEG monitoring may be programmed to provide alerts when a neurological event has exceeded a pre-determined duration or severity.

FIG. 5 is a simplified schematic view of a full Monitor 200 implanted in a patient 10. Monitor 200 continuously senses and monitors cardiac, brain and respiration function of patient 10 via one or more brain monitoring elements 18 and one or more cardiac monitoring elements 14 or one or more respiratory monitoring elements 15. Brain monitoring elements 18 may be for example, one or more brain leads with one or more electrodes. Such a brain lead may be any lead capable of sensing brain activity such as EEG. For example, brain monitoring element 18 may be a deep brain lead, a cortical lead or an electrode placed on the head externally. Cardiac monitoring elements 14 may be cardiac leads or other types of sensors or electrodes capable of picking up cardiac signals. These monitoring elements allow detection of a neurological event and the recording of data and signals pre and post event. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data. An implant aid may be used with Monitor 200 to ensure a proper position and orientation during implant as described above in connection with the system of FIG. 1.

FIG. 6 is a simplified schematic view of a second embodiment of a full Monitor 220 implanted in a patient 10. Monitor 220 continuously senses and monitors cardiac, brain and respiration function of patient 10 via cardiac lead(s) 16 and a brain lead 18 to allow detection of a neurological event and the recording of data and signals pre and post event. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data.

FIG. 7 is a simplified schematic view of a third embodiment of a full Monitor 240 implanted in a patient 10. Monitor 240 continuously senses and monitors cardiac, brain and respiration function of patient 10 via sensor stub 20 and brain lead 18 to allow detection of a neurological event and the recording of data and signals pre and post event. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data.

FIG. 8 is a simplified schematic view of a fourth embodiment of a full Monitor 260 implanted in a patient 10. Monitor 260 in combination with external patch 160 continuously senses and monitors cardiac, brain and respiration function of patient 10 to allow detection of a neurological event and the recording of data and signals pre and post event. A 2-way wireless telemetry communication link 30 connects the Monitor unit 260 and external patch 160. The wireless communication link 30 may consist of an RF link (such as described in U.S. Pat. No. 5,683,432 “Adaptive Performance-Optimizing Communication System for Communicating with an Implantable Medical Device” to Goedeke, et al), an electromagnetic/ionic transmission (such as described in U.S. Pat. No. 4,987,897 “Body Bus Medical Device Communication System” to Funke) or acoustic transmission (such as described in U.S. Pat. No. 5,113,859 “Acoustic Body Bus Medical Device Communication System” to Funke). Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data. Also optionally, a button 38 on the external patch monitor 160 may be activated by the patient 10 to manually activate diagnostic data recording.

An alternative embodiment of the system of FIG. 8 consists of software “patches” or programs downloaded from a wearable patch 38 into an implanted neurostimulator, drug pump or monitor to allow research evaluation of new therapies, detection algorithms, clinical research and data gathering and the use of the patient as their own “control” by randomly downloading or enabling a new detection algorithm or therapy and gathering the resultant clinical data (as substantially described in U.S. Pat. No. 6,200,265 “Peripheral Memory Patch and Access Method for Use with an Implantable Medical Device” to Walsh, et al). The clinical and diagnostic data may be uploaded into the memory of the patch for later retrieval and review by the patient's physician or device clinical manager. This embodiment also allows the upgrading of the existing implant base with temporary new or additional therapeutic and diagnostic features.

FIG. 9 is a simplified schematic view of a fifth embodiment of a full Monitor 280 implanted in a patient 10. Monitor 280 continuously senses and monitors cardiac, brain and respiration function of patient 10 via brain lead 18 with integrated electrode 24 to allow detection of a neurological event and the recording of data and signals pre and post event. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data. Integrated electrode 24 senses ECG signals as described above in the referenced Klein '352 patent and respiration signals as described above in the referenced Plicchi '892 and '251 patents.

FIG. 10 is a simplified schematic view of a sixth embodiment of a full Monitor 26 implanted cranially in a patient 10. Monitor 26 continuously senses and monitors cardiac, brain and respiration function of patient 10 to allow detection of a neurological event and the recording of data and signals pre and post event. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data.

Monitor 26 may be constructed as substantially described in US Publication No. 20040176817 “Modular implantable medical device” to Wahlstrand et al. or U.S. Pat. No. 5,782,891 “Implantable Ceramic Enclosure for Pacing, Neurological and Other Medical Applications in the Human Body” to Hassler, et al or U.S. Pat. No. 6,427,086 “Means and Method for the Intracranial Placement of a Neurostimulator” to Fischell. et al. EEG sensing is accomplished by the use of integrated electrodes in the housing of monitor 26 or, alternatively, by cranially implanted leads.

ECG sensing in the cranium may be accomplished by leadless ECG sensing as described in the above Brabec '940, Ceballos '915 and Lee '067 referenced patents. Alternatively, ECG rate and asystole may be inferred (along with a blood pressure signal) from a capacitive dynamic pressure signal (ie, dP/dt) as substantially described in U.S. Pat. No. 4,485,813 “Implantable Dynamic Pressure Transducer System” to Anderson, et al. ECG rate and asystole may be inferred by monitoring an acoustic signal (i.e., sound) as substantially described in U.S. Pat. No. 5,554,177 “Method and Apparatus to Optimize Pacing Based on Intensity of Acoustic Signal” to Kieval, et al. The sensed acoustic signal is low pass filtered to limit ECG signals to 0.5-3 Hz while filtering out speech, swallowing and chewing sounds. ECG rate and asystole may be inferred (along with a blood saturation measurement) by monitoring a reflectance oximetry signal (i.e., O₂sat) as substantially described in U.S. Pat. No. 4,903,701 “Oxygen Sensing Pacemaker” to Moore, et al. ECG rate and asystole may be inferred by monitoring a blood temperature signal (i.e., dT/dt) as substantially described in U.S. Pat. No. 5,336,244 “Temperature Sensor Based Capture Detection for a Pacer” to Weijand. ECG rate and asystole may be inferred (along with an arterial flow measurement) by monitoring a blood flow signal (from an adjacent vein via impedance plethysmography, piezoelectric sensor or Doppler ultrasound) as substantially described in U.S. Pat. No. 5,409,009 “Methods for Measurement of Arterial Blood Flow” to Olson. ECG rate and asystole may be inferred (along with a blood pressure measurement) by monitoring a blood pressure signal utilizing a strain gauge substantially described in U.S. Pat. No. 5,168,759 “Strain Gauge for. Medical Applications” to Bowman. ECG rate and asystole may be inferred by monitoring a blood parameter sensor (such as oxygen, pulse or flow) located on a V-shaped lead as substantially described in U.S. Pat. No. 5,354,318 “Method and Apparatus for Monitoring Brain Hemodynamics” to Taepke.

Monitor 26 may warn or alert the patient 10 via an annunciator such as buzzes, tones, beeps or spoken voice (as substantially described in U.S. Pat. No. 6,067,473 “Implantable Medical Device Using Audible Sound Communication to Provide Warnings” to Greeninger, et al.) via a piezo-electric transducer incorporated in the housing of monitor 26 and transmitting sound to the patient's 10 inner ear.

Monitor+Treatment (Brain)

FIG. 11 is a simplified schematic view of a full Monitor/Brain Therapy unit 300 implanted in a patient 10. Monitor/Brain Therapy unit 300 continuously senses and monitors cardiac, brain and respiration function of patient 10 via monitoring elements 14 and 18. Such monitoring elements may be subcutaneous electrodes and a brain lead to allow detection of a neurological event, the recording of data and signals pre and post event, and the delivery of therapy via brain lead. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data and delivery of therapy. An implant aid may be used with Monitor/Brain Therapy device 300 to assist with positioning and orientation during implant as described above in connection with the system of FIG. 1.

FIG. 12A is a simplified schematic view of a second embodiment of a full Monitor/Brain Therapy unit 320 implanted in a patient 10. Monitor/Brain Therapy unit 320 continuously senses and monitors cardiac, brain and respiration function of patient 10 via cardiac lead(s) 16 and a brain lead 18 to allow detection of a neurological event, the recording of data and signals pre and post event, and the delivery of therapy via brain lead 18. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data and delivery of therapy.

FIG. 12B is a simplified schematic view of a third embodiment of a full Monitor/Brain Therapy system consisting of a thoracically implanted Monitor unit 321 in combination with a cranially implanted brain Monitor/Therapy unit 26. Monitor unit 321 continuously senses and monitors the cardiac and respiration function of patient 10 via cardiac lead(s) 16 to allow detection of a neurological event, the recording of data and signals pre and post event, and the delivery of therapy via Monitor/Therapy unit 26. A 2-way wireless telemetry communication link 30 connects the Monitor/Therapy unit 26 and cardiac/respiration monitor 321. The wireless communication link 30 may consist of an RF link (such as described in U.S. Pat. No. 5,683,432 “Adaptive Performance-Optimizing Communication System for Communicating with an Implantable Medical Device” to Goedeke, et al ), an electromagnetic/ionic transmission (such as described in U.S. Pat. No. 4,987,897 “Body Bus Medical Device Communication System” to Funke) or acoustic transmission (such as described in U.S. Pat. No. 5,113,859 “Acoustic Body Bus Medical Device Communication System” to Funke). Monitor 26 may be constructed as substantially described in US Publication No. 20040176817 “Modular implantable medical device” to Wahlstrand et al. or U.S. Pat. No. 5,782,891 “Implantable Ceramic Enclosure for Pacing, Neurological and Other Medical Applications in the Human Body” to Hassler, et al or U.S. Pat. No. 6,427,086 “Means and Method for the Intracranial Placement of a Neurostimulator” to Fischell. et al. EEG sensing and brain stimulation is accomplished by the use of integrated electrodes in the housing of Monitor/Therapy unit 26 or, alternatively, by cranially implanted leads (not shown in FIG. 12B). Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data and delivery of therapy.

FIG. 13 is a simplified schematic view of a fourth embodiment of a full Monitor/Brain Therapy unit 340 implanted in a patient 10. Monitor/Brain Therapy unit 340 continuously senses and monitors cardiac, brain and respiration function of patient 10 via sensor stub 20 and a brain lead 18 to allow detection of a neurological event such as a neurological event, the recording of data and signals pre and post event, and the delivery of therapy via brain lead 18. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data and delivery of therapy.

FIG. 14 is a simplified schematic view of a fifth embodiment of a full Monitor/Brain Therapy unit 360 implanted in a patient 10. Monitor/Brain Therapy unit 360 in combination with external patch 160 continuously senses and monitors cardiac, brain and respiration function of patient 10 via external patch 160 and a brain lead 18 to allow detection of neurological events, the recording of data and signals pre and post event, and the delivery of therapy via brain lead 18. A 2-way wireless telemetry communication link 30 connects the Monitor/Brain Therapy unit 360 and external patch 160. The wireless communication link 30 may consist of an RF link (such as described in U.S. Pat. No. 5,683,432 “Adaptive Performance-Optimizing Communication System for Communicating with an Implantable Medical Device” to Goedeke, et al ), an electromagnetic/ionic transmission (such as described in U.S. Pat. No. 4,987,897 “Body Bus Medical Device Communication System” to Funke) or acoustic transmission (such as described in U.S. Pat. No. 5,113,859 “Acoustic Body Bus Medical Device Communication System” to Funke). Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data and delivery of therapy. Also optionally, a button 38 on the external patch monitor 160 may be activated by the patient 10 to manually activate diagnostic data recording and therapy delivery.

FIG. 15 is a simplified schematic view of a sixth embodiment of a full Monitor/Brain Therapy unit 380 implanted in a patient 10. Monitor/Brain Therapy unit 380 continuously senses and monitors cardiac, brain and respiration function of patient 10 via a brain lead 18 with integrated electrode 24 to allow detection of neurological events, the recording of data and signals pre and post event, and the delivery of therapy via brain lead 18. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data and delivery of therapy. Integrated electrode 24 senses ECG signals as described above in the referenced Klein '352 patent and respiration signals as described above in the referenced Plicchi '892 and '251 patents.

FIG. 20 is a simplified schematic view of a seventh embodiment of a full Monitor/Brain Therapy unit 26 implanted cranially in a patient 10. Monitor/Brain Therapy unit 26 in combination with leadless Monitor 400 continuously senses and monitors cardiac, brain and respiration function of patient 10 to allow detection of neurological events, the recording of data and signals pre and post event, and the delivery of therapy via brain lead 18. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data and delivery of therapy. A 2-way wireless telemetry communication link 30 connects the Monitor/Therapy unit 26 and leadless Monitor 400. The wireless communication link 30 may consist of an RF link (such as described in U.S. Pat. No. 5,683,432 “Adaptive Performance-Optimizing Communication System for Communicating with an Implantable Medical Device” to Goedeke, et al ), an electromagnetic/ionic transmission (such as described in U.S. Pat. No. 4,987,897 “Body Bus Medical Device Communication System” to Funke) or acoustic transmission (such as described in U.S. Pat. No. 5,113,859 “Acoustic Body Bus Medical Device Communication System” to Funke). An implant aid may be used with Monitor device 400 to ensure a proper position and orientation during implant as described above in connection with the system of FIG. 1. Monitor 26 may be constructed as substantially described in US Publication No. 20040176817 “Modular implantable medical device” to Wahlstrand et al. or U.S. Pat. No. 5,782,891 “Implantable Ceramic Enclosure for Pacing, Neurological and Other Medical Applications in the Human Body” to Hassler, et al or U.S. Pat. No. 6,427,086 “Means and Method for the Intracranial Placement of a Neurostimulator” to Fischell. et al. EEG sensing is accomplished by the use of integrated electrodes in the housing of monitor 26 or, alternatively, by cranially implanted leads.

Monitor 26 may warn/alert the patient 10 via an annunciator such as, but not limited to, buzzes, tones, beeps or spoken voice (as substantially described in U.S. Pat. No. 6,067,473 “Implantable Medical Device Using Audible Sound Communication to Provide Warnings” to Greeninger, et al.) via a piezo-electric transducer incorporated in the housing of monitor 26 and transmitting sound to the patient's 10 inner ear.

FIG. 21 is a simplified schematic view of an eighth embodiment of a full Monitor/Brain Therapy unit 420 implanted cranially in a patient 10. Monitor/Brain Therapy unit 400 in combination with external patch core monitor 160 continuously senses and monitors cardiac, brain and respiration function of patient 10 to allow detection of neurological events, the recording of data and signals pre and post event, and the delivery of therapy via brain lead 18. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data and delivery of therapy. A 2-way wireless telemetry communication link 30 connects the Monitor/Therapy unit 26 and leadless Monitor 400. The wireless communication link 30 may consist of an RF link (such as described in U.S. Pat. No. 5,683,432 “Adaptive Performance-Optimizing Communication System for Communicating with an Implantable Medical Device” to Goedeke, et al ), an electromagnetic/ionic transmission (such as described in U.S. Pat. No. 4,987,897 “Body Bus Medical Device Communication System” to Funke) or acoustic transmission (such as described in U.S. Pat. No. 5,113,859 “Acoustic Body Bus Medical Device Communication System” to Funke).

Monitor 26 may be constructed as substantially described in US Publication No. 20040176817 “Modular implantable medical device” to Wahlstrand et al. or U.S. Pat. No. 5,782,891 “Implantable Ceramic Enclosure for Pacing, Neurological and Other Medical Applications in the Human Body” to Hassler, et al or U.S. Pat. No. 6,427,086 “Means and Method for the Intracranial Placement of a Neurostimulator” to Fischell. et al. EEG sensing is accomplished by the use of integrated electrodes in the housing of monitor 26 or, alternatively, by cranially implanted leads.

Monitor 26 may warn/alert the patient 10 via an annunciator such as, but not limited to, buzzes, tones, beeps or spoken voice (as substantially described in U.S. Pat. No. 6,067,473 “Implantable Medical Device Using Audible Sound Communication to Provide Warnings” to Greeninger, et al.) via a piezo-electric transducer incorporated in the housing of monitor 26 and transmitting sound to the patient's 10 inner ear.

Monitor+Treatment (Brain+Respiration)

FIG. 16A is a simplified schematic view of a full Monitor/Brain and Respiration Therapy unit 440 implanted in a patient 10. Monitor/Brain and Respiration Therapy unit 440 continuously senses and monitors cardiac, brain and respiration function of patient 10 via cardiac lead(s) 16 and a brain lead 18 to allow detection of neurological events, the recording of data and signals pre and post event, and the delivery of therapy via brain lead 18 and phrenic nerve lead 28. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data and delivery of therapy. Optionally, lead 28 may connect to the diaphragm to provide direct diaphragmatic stimulation.

FIG. 16B is a simplified schematic view of a second embodiment of a full Monitor/Brain and Respiration Therapy system consisting of a thoracically implanted Monitor/Respiration Therapy unit 441 in combination with a cranially implanted brain Monitor/Therapy unit 26. Monitor unit 441 continuously senses and monitors the cardiac and respiration function of patient 10 via cardiac lead(s) 16 to allow detection of neurological events, the recording of data and signals pre and post event, the delivery of respiration therapy via phrenic nerve lead 28 and the delivery of brain stimulation via Monitor/Therapy unit 26. A 2-way wireless telemetry communication link 30 connects the Monitor/Therapy unit 26 and cardiac/respiration monitor and respiration therapy unit 441. The wireless communication link 30 may consist of an RF link (such as described in U.S. Pat. No. 5,683,432 “Adaptive Performance-Optimizing Communication System for Communicating with an Implantable Medical Device” to Goedeke, et al ), an electromagnetic/ionic transmission (such as described in U.S. Pat. No. 4,987,897 “Body Bus Medical Device Communication System” to Funke) or acoustic transmission (such as described in U.S. Pat. No. 5,113,859 “Acoustic Body Bus Medical Device Communication System” to Funke). Monitor 26 may be constructed as substantially described in US Publication No. 20040176817 “Modular implantable medical device” to Wahlstrand et al. or U.S. Pat. No. 5,782,891 “Implantable Ceramic Enclosure for Pacing, Neurological and Other Medical Applications in the Human Body” to Hassler, et al or U.S. Pat. No. 6,427,086 “Means and Method for the Intracranial Placement of a Neurostimulator” to Fischell. et al. EEG sensing and brain stimulation is accomplished by the use of integrated electrodes in the housing of monitor 26 or, alternatively, by cranially implanted leads (not shown in FIG. 16B). Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data and delivery of therapy. Optionally, lead 28 may connect to the diaphragm to provide direct diaphragmatic stimulation.

FIG. 17 is a simplified schematic view of a third embodiment of a full Monitor/Brain and Respiration Therapy unit 460 implanted in a patient 10. Monitor/Brain and Respiration Therapy unit 460 continuously senses and monitors cardiac, brain and respiration function of patient 10 via sensor stub 20 and a brain lead 18 to allow detection of neurological events, the recording of data and signals pre and post event, and the delivery of therapy via brain lead 18 and phrenic nerve lead 28. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data and delivery of therapy. Optionally, lead 28 may connect to the diaphragm to provide direct diaphragmatic stimulation.

FIG. 18 is a simplified schematic view of a fourth embodiment of a full Monitor/Brain and Respiration Therapy unit 480 implanted in a patient 10. Monitor/Brain and Respiration Therapy unit 480 continuously senses and monitors cardiac, brain and respiration function of patient 10 via a brain lead 18 with integrated electrode 24 to allow detection of neurological events, the recording of data and signals pre and post event, and the delivery of therapy via brain lead 18 and phrenic nerve lead 28. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data and delivery of therapy. Optionally, lead 28 may connect to the diaphragm to provide direct diaphragmatic stimulation. Integrated electrode 24 senses ECG signals as described above in the referenced Klein '352 patent and respiration signals as described above in the referenced Plicchi '892 and '251 patents.

FIG. 19 is a simplified schematic view of a fifth embodiment of a full Monitor/Brain and Respiration Therapy unit 500 implanted in a patient 10. Monitor/Brain and Respiration Therapy unit 500 continuously senses and monitors cardiac, brain and respiration function of patient 10 via brain lead 18 and respiration lead 28 with integrated electrode 24 to allow detection of neurological events, the recording of data and signals pre and post event, and the delivery of therapy via brain lead 18 and phrenic nerve lead 28. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data and delivery of therapy. Optionally, lead 28 may connect to the diaphragm to provide direct diaphragmatic stimulation. Integrated electrode 24 senses ECG signals as described above in the referenced Klein '352 patent and respiration signals as described above in the referenced Plicchi '892 and '251 patents.

Monitor+Treatment (Brain+Cardiac)

FIG. 24A is a simplified schematic view of a full Monitor/Brain and Cardiac Therapy unit 520 implanted in a patient 10. Monitor/Brain and Cardiac Therapy unit 520 continuously senses and monitors cardiac, brain and respiration function of patient 10 via cardiac lead(s) 16 and a brain lead 18 to allow detection of neurological events, the recording of data and signals pre and post event, and the delivery of therapy via brain lead 18 and cardiac lead(s) 16. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data and delivery of therapy.

FIG. 24B is a simplified schematic view of a second embodiment of a full Monitor/Brain and Cardiac Therapy system consisting of a thoracically implanted Monitor/Therapy unit 521 implanted in patient 10 in combination with a cranially implanted brain Monitor/Therapy unit 26. Monitor/Therapy unit 521 continuously senses and monitors the cardiac and respiration function of patient 10 via cardiac lead(s) 16 to allow detection of neurological events, the recording of data and signals pre and post event, the delivery of cardiac therapy via Monitor/Therapy unit 521 and the delivery of therapy via Monitor/Therapy unit 26. A 2-way wireless telemetry communication link 30 connects the Monitor/Therapy unit 26 and cardiac/respiration Monitor/Therapy unit 521. The wireless communication link 30 may consist of an RF link (such as described in U.S. Pat. No. 5,683,432 “Adaptive Performance-Optimizing Communication System for Communicating with an Implantable Medical Device” to Goedeke, et al ), an electromagnetic/ionic transmission (such as described in U.S. Pat. No. 4,987,897 “Body Bus Medical Device Communication System” to Funke) or acoustic transmission (such as described in U.S. Pat. No. 5,113,859 “Acoustic Body Bus Medical Device Communication System” to Funke). Monitor 26 may be constructed as substantially described in US Publication No. 20040176817 “Modular implantable medical device” to Wahlstrand et al. or U.S. Pat. No. 5,782,891 “Implantable Ceramic Enclosure for Pacing, Neurological and Other Medical Applications in the Human Body” to Hassler, et al or U.S. Pat. No. 6,427,086 “Means and Method for the Intracranial Placement of a Neurostimulator” to Fischell. et al. EEG sensing and brain stimulation is accomplished by the use of integrated electrodes in the housing of monitor 26 or, alternatively, by cranially implanted leads (not shown in FIG. 24B). Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data and delivery of therapy.

FIG. 22 is a simplified schematic view of a third embodiment of a full Monitor/Brain and Cardiac Therapy unit 540 implanted cranially in a patient 10. Monitor/Brain and Cardiac Therapy unit 540 in combination with external patient worn vest 34 continuously senses and monitors cardiac, brain and respiration function of patient 10 to allow detection of neurological events, the recording of data and signals pre and post event, and the delivery of therapy via brain lead 18 and vest 34. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data and delivery of therapy. A 2-way wireless telemetry communication link 30 connects the monitor/therapy unit 540 and patient worn vest 34. The wireless communication link 30 may consist of an RF link (such as described in U.S. Pat. No. 5,683,432 “Adaptive Performance-Optimizing Communication System for Communicating with an Implantable Medical Device” to Goedeke, et al ), an electromagnetic/ionic transmission (such as described in U.S. Pat. No. 4,987,897 “Body Bus Medical Device Communication System” to Funke) or acoustic transmission (such as described in U.S. Pat. No. 5,113,859 “Acoustic Body Bus Medical Device Communication System” to Funke).

Monitor/Therapy unit 540 may be constructed as substantially described in US Publication No. 20040176817 “Modular implantable medical device” to Wahlstrand et al. or U.S. Pat. No. 5,782,891 “Implantable Ceramic Enclosure for Pacing, Neurological and Other Medical Applications in the Human Body” to Hassler, et al or U.S. Pat. No. 6,427,086 “Means and Method for the Intracranial Placement of a Neurostimulator” to Fischell. et al. EEG sensing is accomplished by the use of integrated electrodes in the housing of Monitor/Therapy unit 540 or, alternatively, by cranially implanted leads.

Monitor/Therapy unit 540 may warn/alert the patient 10 via an annunciator such as, but not limited to, buzzes, tones, beeps or spoken voice (as substantially described in U.S. Pat. No. 6,067,473 “Implantable Medical Device Using Audible Sound Communication to Provide Warnings” to Greeninger, et al.) via a piezo-electric transducer incorporated in the housing of monitor 26 and transmitting sound to the patient's 10 inner ear.

FIG. 23 is a simplified schematic view of a fourth embodiment of a full Monitor/Brain and Cardiac Therapy unit 560 implanted cranially in a patient 10. Monitor/Brain and Cardiac Therapy unit 560 in combination with leadless defibrillator 36 continuously senses and monitors cardiac, brain and respiration function of patient 10 to allow detection of neurological events, the recording of data and signals pre and post event, and the delivery of therapy via brain lead 18 and defibrillator 36. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data and delivery of therapy. A 2-way wireless telemetry communication link 30 connects the monitor/therapy unit 560 and leadless defibrillator 36. The wireless communication link 30 may consist of an RF link (such as described in U.S. Pat. No. 5,683,432 “Adaptive Performance-Optimizing Communication System for Communicating with an Implantable Medical Device” to Goedeke, et al ), an electromagnetic/ionic transmission (such as described in U.S. Pat. No. 4,987,897 “Body Bus Medical Device Communication System” to Funke) or acoustic transmission (such as described in U.S. Pat. No. 5,113,859 “Acoustic Body Bus Medical Device Communication System” to Funke).

Monitor/Therapy unit 560 may be constructed as substantially described in US Publication No. 20040176817 “Modular implantable medical device” to Wahlstrand et al. or U.S. Pat. No. 5,782,891 “Implantable Ceramic Enclosure for Pacing, Neurological and Other Medical Applications in the Human Body” to Hassler, et al or U.S. Pat. No. 6,427,086 “Means and Method for the Intracranial Placement of a Neurostimulator” to Fischell. et al. EEG sensing is accomplished by the use of integrated electrodes in the housing of Monitor/Therapy unit 560 or, alternatively, by cranially implanted leads.

Monitor/Therapy unit 560 may warn/alert the patient 10 via an annunciator such as, but not limited to, buzzes, tones, beeps or spoken voice (as substantially described in U.S. Pat. No. 6,067,473 “Implantable Medical Device Using Audible Sound Communication to Provide Warnings” to Greeninger, et al.) via a piezo-electric transducer incorporated in the housing of Monitor/Therapy unit 560 and transmitting sound to the patient's 10 inner ear.

Monitor+Treatment (Brain+Respiration+Cardiac)

FIG. 25A is a simplified schematic view of a full Monitor/Brain, Respiration and Cardiac Therapy unit 580 implanted in a patient 10. Monitor/Brain, Respiration and Cardiac Therapy unit 580 continuously senses and monitors cardiac, brain and respiration function of patient 10 via cardiac lead(s) 16 and a brain lead 18 to allow detection of neurological events, the recording of data and signals pre and post event, and the delivery of therapy via brain lead 18, cardiac lead(s) 16 and phrenic nerve lead 28. Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data and delivery of therapy. Optionally, lead 28 may connect to the diaphragm to provide direct diaphragmatic stimulation.

FIG. 25B is a simplified schematic view of a second embodiment of a full Monitor/Brain, Respiration and Cardiac Therapy system consisting of a thoracically implanted Monitor/Respiration Therapy unit 581 in combination with a cranially implanted brain Monitor/Therapy unit 26. Monitor/Therapy unit 581 continuously senses and monitors the cardiac and respiration function of patient 10 via cardiac lead(s) 16 to allow detection of neurological events, the recording of data and signals pre and post event, the delivery of respiration therapy via phrenic nerve lead 28 and the delivery of brain stimulation via Monitor/Therapy unit 26. A 2-way wireless telemetry communication link 30 connects the Monitor/Therapy unit 26 and cardiac/respiration monitor/therapy unit 581. The wireless communication link 30 may consist of an RF link (such as described in U.S. Pat. No. 5,683,432 “Adaptive Performance-Optimizing Communication System for Communicating with an Implantable Medical Device” to Goedeke, et al ), an electromagnetic/ionic transmission (such as described in U.S. Pat. No. 4,987,897 “Body Bus Medical Device Communication System” to Funke) or acoustic transmission (such as described in U.S. Pat. No. 5,113,859 “Acoustic Body Bus Medical Device Communication System” to Funke). Monitor 26 may be constructed as substantially described in US Publication No. 20040176817 “Modular implantable medical device” to Wahlstrand et al. or U.S. Pat. No. 5,782,891 “Implantable Ceramic Enclosure for Pacing, Neurological and Other Medical Applications in the Human Body” to Hassler, et al or U.S. Pat. No. 6,427,086 “Means and Method for the Intracranial Placement of a Neurostimulator” to Fischell. et al. EEG sensing and brain stimulation is accomplished by the use of integrated electrodes in the housing of monitor 26 or, alternatively, by cranially implanted leads (not shown in FIG. 25B). Stored diagnostic data is uplinked and evaluated by the patient's physician utilizing programmer 12 via a 2-way telemetry link 32. An external patient activator 22 may optionally allow the patient 10, or other care provider (not shown), to manually activate the recording of diagnostic data and delivery of therapy. Optionally, lead 28 may connect to the diaphragm to provide direct diaphragmatic stimulation.

Core Monitor Design

Turning now to FIG. 26, there is shown a block diagram of the electronic circuitry that makes up core Monitor 100 (FIG. 1) in accordance with one embodiment of the invention. As can be seen from FIG. 26, Monitor 100 comprises a primary control circuit 720. Much of the circuitry associated with primary control circuit 720 is of conventional design, in accordance, for example, with what is disclosed in U.S. Pat. No. 5,052,388 to Sivula et al, entitled “Method and Apparatus for Implementing Activity Sensing in a Pulse Generator.” To the extent that certain components of Monitor 100 are purely conventional in their design and operation, such components will not be described herein in detail, as it is believed that design and implementation of such components would be a matter of routine to those of ordinary skill in the art. For example, primary control circuit 720 in FIG. 26 includes sense amplifier circuitry 724, a crystal clock 728, a random-access memory and read-only memory (RAM/ROM) unit 730, a central processing unit (CPU) 732, a MV Processor circuit 738 and a telemetry circuit 734, all of which are well-known in the art.

Monitor 100 preferably includes internal telemetry circuit 734 so that it is capable of being programmed by means of external programmer/control unit 12 via a 2-way telemetry link 32 (shown in FIG. 1). Programmers and telemetry systems suitable for use in the practice of the present invention have been well known for many years. Known programmers typically communicate with an implanted device via a bi-directional radio-frequency telemetry link, so that the programmer can transmit control commands and operational parameter values to be received by the implanted device, and so that the implanted device can communicate diagnostic and operational data to the programmer. Programmers believed to be suitable for the purposes of practicing the present invention include the Models 9790 and CareLink® programmers, commercially available from Medtronic, Inc., Minneapolis, Minn. Various telemetry systems for providing the necessary communications channels between an external programming unit and an implanted device have been developed and are well known in the art. Telemetry systems believed to be suitable for the purposes of practicing the present invention are disclosed, for example, in the following U.S. Patents: U.S. Pat. No. 5,127,404 to Wyborny et al. entitled “Telemetry Format for Implanted Medical Device”; U.S. Pat. No. 4,374,382 to Markowitz entitled “Marker Channel Telemetry System for a Medical Device”; and U.S. Pat. No. 4,556,063 to Thompson et al. entitled “Telemetry System for a Medical Device”.

Typically, telemetry systems such as those described in the above referenced patents are employed in conjunction with an external programming/processing unit. Most commonly, telemetry systems for implantable medical devices employ a radio-frequency (RF) transmitter and receiver in the device, and a corresponding RF transmitter and receiver in the external programming unit. Within the implantable device, the transmitter and receiver utilize a wire coil as an antenna for receiving downlink telemetry signals and for radiating RF signals for uplink telemetry. The system is modeled as an air-core coupled transformer. An example of such a telemetry system is shown in the above-referenced Thompson et al. '063 patent.

In order to communicate digital data using RF telemetry, a digital encoding scheme such as is described in the above-reference Wyborny et al. '404 patent can be used. In particular, for downlink telemetry a pulse interval modulation scheme may be employed, wherein the external programmer transmits a series of short RF “bursts” or pulses in which the interval between successive pulses (e.g., the interval from the trailing edge of one pulse to the trailing edge of the next) is modulated according to the data to be transmitted. For example, a shorter interval may encode a digital “0” bit while a longer interval encodes a digital “1” bit.

For uplink telemetry, a pulse position modulation scheme may be employed to encode uplink telemetry data. For pulse position modulation, a plurality of time slots are defined in a data frame, and the presence or absence of pulses transmitted during each time slot encodes the data. For example, a sixteen-position data frame may be defined, wherein a pulse in one of the time slots represents a unique four-bit portion of data.

As depicted in FIG. 26, programming units such as the above-referenced Medtronic Models 9790 and CareLink® programmers typically interface with the implanted device through the use of a programming head or programming paddle, a handheld unit adapted to be placed on the patient's body over the implant site of the patient's implanted device. A magnet in the programming head effects reed switch closure in the implanted device to initiate a telemetry session. Thereafter, uplink and downlink communication takes place between the implanted device's transmitter and receiver and a receiver and transmitter disposed within the programming head.

As previously noted, primary control circuit 720 includes central processing unit 732 which may be an off-the-shelf programmable microprocessor or microcontroller, but in the presently preferred embodiment of the invention is a custom integrated circuit. Although specific connections between CPU 732 and other components of primary control circuit 720 are not shown in FIG. 26, it will be apparent to those of ordinary skill in the art that CPU 732 functions to control the timed operation of sense amplifier circuit 724 under control of programming stored in RAM/ROM unit 730. It is believed that those of ordinary skill in the art will be familiar with such an operative arrangement.

With continued reference to FIG. 26, crystal oscillator circuit 728, in the presently preferred embodiment a 32,768-Hz crystal controlled oscillator, provides main timing clock signals to primary control circuit 720.

It is to be understood that the various components of monitor 100 depicted in FIG. 26 are powered by means of a battery (not shown), which is contained within the hermetic enclosure of monitor 100, in accordance with common practice in the art. For the sake of clarity in the figures, the battery and the connections between it and the other components of monitor 100 are not shown.

With continued reference to FIG. 26, sense amplifier 724 is coupled to monitoring elements 14 such as subcutaneous electrodes. Cardiac intrinsic signals are sensed by sense amplifier 724 as substantially described in U.S. Pat. No. 6,505,067 “System and Method for Deriving a Virtual ECG or EGM Signal” to Lee, et al. Further processing by CPU 732 allows the detection of cardiac electrical characteristics/anomalies (e.g., heart rate, heart rate variability, arrhythmias, cardiac arrest, sinus arrest and sinus tachycardia) that would be a matter of routine to those of ordinary skill in the art.

Further processing of the cardiac signal amplitudes may be used to detect respiration characteristics/anomalies (e.g., respiration rate, tidal volume, minute ventilation, and apnea) in MV Processor 738. FIG. 27 shows the intracardiac signals 770 presented to sense amplifier 724 from monitoring elements 14. Note the amplitude variation of cardiac signals caused by the change in thoracic cavity pressure due to respiration (ie, inspiration and expiration). By low pass filtering the cardiac signals 770, a signal representing minute ventilation may be obtained as depicted in waveform 772 (FIG. 27). This respiration signal may further be examined to detect respiration rate and reduced or absence of inspiration and expiration (central apnea) by CPU 732 and software resident in RAM/ROM 730.

Upon detection of either a cardiac or respiration anomaly, CPU 732, under control of computer executable instruction in firmware resident in RAM/ROM 730, will initiate recording of the appropriate diagnostic information into RAM of RAM/ROM 730, initiate a warning or alert to the patient, patient caregiver, or remote monitoring location. See flow diagram and description as described below in association with FIG. 31.

Turning now to FIG. 28, there is shown a block diagram of the electronic circuitry that makes up core Monitor 120 (FIG. 2) in accordance with another disclosed embodiment of the invention. As can be seen from FIG. 28, Monitor 120 comprises a primary control circuit 720 and a minute ventilation circuit 722. Much of the circuitry associated with primary control circuit 720 is of conventional design, in accordance, for example, with what is disclosed in U.S. Pat. No. 5,052,388 to Sivula et al, entitled “Method and Apparatus for Implementing Activity Sensing in a Pulse Generator.” To the extent that certain components of Monitor 120 are purely conventional in their design and operation, such components will not be described herein in detail, as it is believed that design and implementation of such components would be a matter of routine to those of ordinary skill in the art. For example, primary control circuit 720 in FIG. 28 includes sense amplifier circuitry 724, a crystal clock 728, a random-access memory and read-only memory (RAM/ROM) unit 730, a central processing unit (CPU) 732, and a telemetry circuit 734, all of which are well-known in the art.

Monitor 120 preferably includes internal telemetry circuit 734 so that it is capable of being programmed by means of external programmer/control unit 12 via a 2-way telemetry link 32 (shown in FIG. 2). Programmers and telemetry systems suitable for use in the practice of the present invention have been well known for many years. Known programmers typically communicate with an implanted device via a bi-directional radio-frequency telemetry link, so that the programmer can transmit control commands and operational parameter values to be received by the implanted device, and so that the implanted device can communicate diagnostic and operational data to the programmer. Programmers believed to be suitable for the purposes of practicing the present invention include the Models 9790 and CareLink® programmers, commercially available from Medtronic, Inc., Minneapolis, Minn. Various telemetry systems for providing the necessary communications channels between an external programming unit and an implanted device have been developed and are well known in the art. Telemetry systems believed to be suitable for the purposes of practicing the present invention are disclosed, for example, in the following U.S. Patents: U.S. Pat. No. 5,127,404 to Wyborny et al. entitled “Telemetry Format for Implanted Medical Device”; U.S. Pat. No. 4,374,382 to Markowitz entitled “Marker Channel Telemetry System for a Medical Device”; and U.S. Pat. No. 4,556,063 to Thompson et al. entitled “Telemetry System for a Medical Device”.

Typically, telemetry systems such as those described in the above referenced patents are employed in conjunction with an external programming/processing unit. Most commonly, telemetry systems for implantable medical devices employ a radio-frequency (RF) transmitter and receiver in the device, and a corresponding RF transmitter and receiver in the external programming unit. Within the implantable device, the transmitter and receiver utilize a wire coil as an antenna for receiving downlink telemetry signals and for radiating RF signals for uplink telemetry. The system is modeled as an air-core coupled transformer. An example of such a telemetry system is shown in the above-referenced Thompson et al. '063 patent.

In order to communicate digital data using RF telemetry, a digital encoding scheme such as is described in the above-reference Wyborny et al. '404 patent can be used. In particular, for downlink telemetry a pulse interval modulation scheme may be employed, wherein the external programmer transmits a series of short RF “bursts” or pulses in which the interval between successive pulses (e.g., the interval from the trailing edge of one pulse to the trailing edge of the next) is modulated according to the data to be transmitted. For example, a shorter interval may encode a digital “0” bit while a longer interval encodes a digital “1” bit.

For uplink telemetry, a pulse position modulation scheme may be employed to encode uplink telemetry data. For pulse position modulation, a plurality of time slots are defined in a data frame, and the presence or absence of pulses transmitted during each time slot encodes the data. For example, a sixteen-position data frame may be defined, wherein a pulse in one of the time slots represents a unique four-bit portion of data.

As depicted in FIG. 28, programming units such as the above-referenced Medtronic Models 9790 and CareLink® programmers typically interface with the implanted device through the use of a programming head or programming paddle, a handheld unit adapted to be placed on the patient's body over the implant site of the patient's implanted device. A magnet in the programming head effects reed switch closure in the implanted device to initiate a telemetry session. Thereafter, uplink and downlink communication takes place between the implanted device's transmitter and receiver and a receiver and transmitter disposed within the-programming head.

With continued reference to FIG. 28, Monitor 120 is coupled to leads 16 which, when implanted, extend transvenously between the implant site of Monitor 120 and the patient's heart (not shown). For the sake of clarity, the connections between leads 16 and the various components of Monitor 120 are not shown in FIG. 28, although it will be clear to those of ordinary skill in the art that, for example, leads 16 will necessarily be coupled, either directly or indirectly, to sense amplifier circuitry 724 in accordance with common practice, such that cardiac electrical signals may be conveyed to sensing circuitry 724, via leads 16. Cardiac leads 16 may consist of any typical lead configuration as is known in the art, such as, without limitation, right ventricular (RV) pacing or defibrillation leads, right atrial (RA) pacing or defibrillation leads, single pass RA/RV pacing or defibrillation leads, coronary sinus (CS) pacing or defibrillation leads, left ventricular pacing or defibrillation leads, pacing or defibrillation epicardial leads, subcutaneous defibrillation leads, unipolar or bipolar lead configurations, or any combinations of the above lead systems.

Sensed cardiac events are evaluated by CPU 732 and software stored in RAM/ROM unit 730. Cardiac anomalies detected include heart rate variability, QT variability, QT_(C), sinus arrest, syncope, ST segment elevation and various arrhythmias such as sinus, atrial and ventricular tachycardias.

Heart rate variability may be measured by the method and apparatus as described in U.S. Pat. No. 5,749,900 “Implantable Medical Device Responsive to Heart Rate Variability Analysis” to Schroeppel, et al and U.S. Pat. No. 6,035,233 “Implantable Medical Device Responsive to Heart Rate Variability Analysis” to Schroeppel, et al. Schroeppel '900 and '233 patents describe an implantable cardiac device that computes time intervals occurring between successive heartbeats and then derive a measurement of heart rate variability from epoch data for predetermined time periods. The Schroeppel device then compares measurement of heart rate variability with previously stored heart rate variability zones, which define normal and abnormal heart rate variability.

QT variability may be measured by the method and apparatus as described in U.S. Pat. No. 5,560,368 “Methodology for Automated QT Variability Measurement” to Berger. The Berger '368 patent utilizes a “stretchable” QT interval template started at the beginning of the QRS complex and terminating on the T-wave to determine beat-to-beat variability.

QT_(C) may be measured by the method and apparatus as described in U.S. Pat. No. 6,721,599 “Pacemaker with Sudden Rate Drop Detection Based on QT Variations” to de Vries. The de Vries '599 patent measures QT interval real time and compares the instantaneous value to a calculated mean via a preprogrammed threshold change value.

Syncope may be detected by the methods and apparatus as described in U.S. Pat. No. 6,721,599 “Pacemaker with Sudden Rate Drop Detection Based on QT Variations” to de Vries. The de Vries '599 patent utilizes a sudden rate change and a real time QT interval measurement compared to a QT mean to detect sudden rate drop and neurally mediated syncope.

ST segment elevation (an indicator of myocardial ischemia) may be detected by the methods and apparatus as described in U.S. Pat. No. 6,128,526 “Method for Ischemia Detection and Apparatus for Using Same” to Stadler, et al and U.S. Pat. No. 6,115,630 “Determination of Orientation of Electrocardiogram Signal in Implantable Medical devices” to Stadler, et al. The Stadler '526 and '630 patents describe a system that compares a sampled data point prior to an R-wave complex peak amplitude to multiple samples post R-wave event to detect ST segment elevation.

Arrhythmias such as sinus, atrial and ventricular tachycardias may be detected by the methods and apparatus as described in U.S. Pat. No. 5,545,186 “Prioritized Rule Based Method and Apparatus for Diagnosis and Treatment of Arrhythmias” to Olson, et al.

Sinus arrest may be detected by the methods and apparatus as described above in the Olson '186 patent.

In the presently disclosed embodiment, two leads are employed—an atrial lead 16A having atrial TIP and RING electrodes, and a ventricular lead 16V having ventricular TIP and RING electrodes. In addition, as noted above, the conductive hermetic canister of Monitor 120 serves as an indifferent electrode.

As previously noted, primary control circuit 720 includes central processing unit 732 which may be an off-the-shelf programmable microprocessor or microcontroller, but in the presently preferred embodiment of the invention is a custom integrated circuit. Although specific connections between CPU 732 and other components of primary control circuit 720 are not shown in FIG. 28, it will be apparent to those of ordinary skill in the art that CPU 732 functions to control the timed operation of sense amplifier circuit 724 under control of programming stored in RAM/ROM unit 730. It is believed that those of ordinary skill in the art will be familiar with such an operative arrangement.

With continued reference to FIG. 28, crystal oscillator circuit 728, in the presently preferred embodiment a 32,768-Hz crystal controlled oscillator, provides main timing clock signals to primary control circuit 720 and to minute ventilation circuit 722.

It is to be understood that the various components of Monitor 120 depicted in FIG. 28 are powered by means of a battery (not shown), which is contained within the hermetic enclosure of Monitor 120, in accordance with common practice in the art. For the sake of clarity in the figures, the battery and the connections between it and the other components of Monitor 120 are not shown.

As shown in FIG. 28, primary control circuit 720 is coupled to minute ventilation circuit 722 by means of multiple signal lines, designated collectively as 738 in FIG. 28. An I/O interface 740 in primary control circuit 720 and a corresponding I/O interface 742 in minute ventilation circuit 722, coordinate the transmission of signals between the two units via control lines 738.

Minute ventilation circuit 722 measures changes in transthoracic impedance, which has been shown to be proportional to minute ventilation. Minute ventilation is the product of tidal volume and respiration rate, and as such is a physiologic indicator of changes in metabolic demand.

Monitor 120, in accordance with the presently disclosed embodiment of the invention, measures transthoracic impedance using a bipolar lead 16 and a tripolar measurement system. As will be hereinafter described in greater detail, minute ventilation circuit 722 delivers 30-microSec biphasic current excitation pulses of 1-mA (peak-to-peak) between a RING electrode of bipolar lead 16 and the conductive canister of monitor 120, functioning as an indifferent electrode CASE, at a rate of 16-Hz. The resulting voltage is then measured between a TIP electrode of lead 16 and the monitor 120 CASE electrode. Such impedance measurement may be programmed to take place in either the atrium or ventricle of the patient's heart.

The impedance signal derived by minute ventilation circuit 722 has three main components: a DC offset voltage; a cardiac component resulting from the heart's function; and a respiratory component. The frequencies of the cardiac and respiratory components are assumed to be identical to their physiologic origin. Since the respiratory component of the impedance signal derived by minute ventilation circuit 722 is of primary interest for this aspect of the present invention, the impedance signal is subjected to filtering in minute ventilation low-pass filter (MV LPF) 750 having a passband of 0.05- to 0.8-Hz (corresponding to 3-48 breaths per minute) to remove the DC and cardiac components.

With continuing reference to FIG. 28, minute ventilation circuit 722 includes a Lead Interface circuit 744 which is essentially a multiplexer that functions to selectively couple and decouple minute ventilation circuit 722 to the VTIP, VRING, ATIP, ARING, and CASE electrodes, as will be hereinafter described in greater detail.

Coupled to lead interface circuit 744 is a minute ventilation (MV) Excitation circuit 746 which functions to deliver the biphasic constant-current pulses between various combinations of lead electrodes (VTIP, VRING, etc.) for the purpose of measuring cardiac impedance. In particular, MV Excitation circuit 746 delivers biphasic excitation pulses (at a rate of 16-Hz between the ventricular ring electrode VRING and the pacemaker canister CASE) of the type delivered in accordance with the method and apparatus described in U.S. Pat. No. 5,271,395 “Method and Apparatus for Rate Responsive Cardiac Pacing” to Wahlstrand et al.

To measure cardiac impedance, minute ventilation circuit 722 monitors the voltage differential present between pairs of electrodes as excitation pulses are being injected as described above. Again, the electrodes from which voltage differentials are monitored will vary depending upon whether atrial or ventricular measurements are being made. In one embodiment of the invention, the same electrodes (i.e., VRING and CASE for ventricular, ARING and CASE for atrial) are used for both delivery of excitation pulses and voltage differential monitoring. It is contemplated, however, that the electrode combinations for excitation and measurement may be among the programmable settings, which may be altered post-implant with the programming system.

With continued reference to FIG. 28, the 16-Hz sampled output voltages from ZMEAS PREAMP circuit 748 are presented to the minute ventilation low-pass filter circuit MV LPF 750, which has a passband of 0.05-0.8 Hz in the presently preferred embodiment of the invention. Again, it is believed that the design and implementation of MV LPF circuit 750 would be a matter of routine engineering to those of ordinary skill in the art. The output from MV LPF circuit 750 is a voltage waveform whose level at any given time is directly proportional to cardiac impedance measured between the selected electrodes. Thus, the MV LPF output signal will be referred to herein as an impedance waveform. MV Calculation 752 analyzes the impedance waveform to determine/detect respiration rate, tidal volume, minute ventilation and presence of apnea.

The circuit of FIG. 28 may additionally monitor pulmonary edema by measuring the DC impedance between the distal electrodes of cardiac leads 16 and the case of core monitor 120. Measurement technique may be as substantially described in U.S. Pat. No. 6,512,949 “Implantable Medical Device for Measuring Time Varying Physiologic Conditions Especially Edema and for Responding Thereto” by Combs, et al.

Upon detection of a cardiac or respiration anomaly, CPU 732, under control of firmware resident in RAM/ROM 730, will initiate recording of the appropriate diagnostic information into RAM of RAM/ROM 730, initiate a warning or alert to the patient, patient caregiver, or remote monitoring location. See flow diagram and description as described below in association with FIG. 31.

Turning now to FIG. 29, there is shown a block diagram of the electronic circuitry that makes up core Monitor 140 with sensor stub 20 (FIG. 3) in accordance with another disclosed embodiment of the invention. As can be seen from FIG. 29, Monitor 140 comprises a primary control circuit 720 and a minute ventilation circuit 722, the function of which has been described in detail above in conjunction with the system of FIG. 28. Monitor 140 measures thoracic impedance from the case of monitor 140 to the distal end of a sensor stub lead 20 (a subcutaneously implanted sensor lead) via an impedance/voltage converter using a sampling frequency of approximately 16 Hz as substantially described in U.S. Pat. No. 4,596,251 “Minute Ventilation Dependant Rate Responsive Pacer” to Plicchi, et al. Respiration parameters are evaluated by CPU 732 and software resident in RAM/ROM 730.

Cardiac signals are sensed by sense amplifier 724 and evaluated by CPU 732 and software resident in RAM/ROM 730.

Upon detection of either/or a cardiac or respiration anomaly, CPU 732, under control of firmware resident in RAM/ROM 730, will initiate recording of the appropriate diagnostic information into RAM of RAM/ROM 730, initiate a warning or alert to the patient, patient caregiver, or remote monitoring location. See flow diagram and description as described below in association with FIG. 31.

Turning now to FIG. 30, there is shown a block diagram of the electronic circuitry that makes up external patch core Monitor 160 (FIG. 4) in accordance with another disclosed embodiment of the invention. As can be seen from FIG. 30, Monitor 160 comprises a primary control circuit 720 and a minute ventilation circuit 722, the function of which has been described in detail above in conjunction with the system of FIG. 28. Intrinsic cardiac signals are sensed by electrodes 161 affixed to the patient's skin, amplified by amplifier 724 and processed by CPU 732 and software program resident in RAM/ROM 730. Cardiac anomalies are detected such as heart rate variability, QT variability, QT_(C), sinus arrest, and various arrhythmias such as sinus, atrial and ventricular tachycardias. Respiration sensing is accomplished by low pass filtering the sensed and amplified intrinsic cardiac signals as shown in FIG. 27. Respiration anomalies (such as reduced or cessation of tidal volume and apnea) are evaluated and detected by CPU 732 and software resident in RAM/ROM 730.

Upon detection of either/or a cardiac or respiration anomaly, CPU 732, under control of firmware resident in RAM/ROM 730, will initiate recording of the appropriate diagnostic information into RAM of RAM/ROM 730, initiate a warning or alert to the patient, patient caregiver, or remote monitoring location. See flow diagram and description as described below in association with FIG. 31.

FIG. 31 is a flow diagram 800 showing operation of a core Monitor sensing/monitoring cardiac and respiration parameters for the detection of neurological events as shown and described in embodiments in FIGS. 1-4 above. Beginning at block 802, the interval between sensed cardiac signals are measured. At block 804, a rate stability measurement is made on each cardiac interval utilizing a heart rate average from block 806. At block 808, a rate stable decision is made based upon preprogrammed parameters. If YES, the flow diagram returns to the HR Measurement block 802. If NO, the rate stability information is provided to Format Diagnostic Data block 812.

At block 816, thoracic impedance is continuously measured in a sampling operation. At block 818, a MV and respiration rate calculation is made. At block 822, a pulmonary apnea decision is made based upon preprogrammed criteria. If NO, the flow diagram returns to MV Measurement block 816. If YES, the occurrence of apnea and MV information is provided to Format Diagnostic Data block 812. Format Diagnostic Data block 812 formats the data from the cardiac and respiration monitoring channels, adds a time stamp (ie, date and time) and provides the data to block 814 where the data is stored in RAM, SRAM or MRAM memory for later retrieval by a clinician via telemetry. Optionally, block 812 may add examples of intrinsic ECG or respiration signals recorded during a sensed episode/seizure. Additionally, optionally, block 815 may initiate a warning or alert to the patient, patient caregiver, or remote monitoring location (as described in U.S. Pat. No. 5,752,976 “World Wide Patient Location and Data Telemetry System for Implantable Medical Devices” to Duffin, et al.

Full Monitor Design

FIG. 32 is a block diagram of the electronic circuitry that makes up full Monitor 200 (FIG. 5) in accordance with the presently disclosed alternative embodiment of the invention. As can be seen from FIG. 32, Monitor 200 includes a primary control circuit 720 that is described herein above in conjunction with FIG. 26. In addition the full monitor of FIG. 30 also includes an amplifier 725 to amplify and sense EEG signals from a cranially implanted lead 18. The CPU 732, in conjunction with a software program resident in RAM/ROM 730, evaluates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, may perform one or more algorithms or methods as described in this specification (such as determination of concordance between EEG and cardiac or respiratory signals, comparison of heart rates associated with certain neurological event time periods, etc.), formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description below in association with FIG. 37.

FIG. 33 is a block diagram of the electronic circuitry that makes up full Monitor 220 with brain 18 and cardiac 16 leads (FIG. 6) in accordance with the presently disclosed alternative embodiment of the invention. As can be seen from FIG. 33, Monitor 220 comprises a primary control circuit 720 and MV circuit 722 that are described herein above in conjunction with FIG. 28. In addition, the full Monitor 220 of FIG. 33 also includes an amplifier 725 to amplify and sense EEG signals from a cranially implanted lead 18. The CPU 732, in conjunction with a software program resident in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description as described below in association with FIG. 37.

FIG. 34 is a block diagram of the electronic circuitry that makes up full Monitor 240 with a brain lead 18 and sensor stub 20 (FIG. 7) in accordance with the presently disclosed alternative embodiment of the invention. As can be seen from FIG. 34, Monitor 240 comprises a primary control circuit 720 and MV circuit 722 that are described herein above in conjunction with FIG. 28. In addition, the full Monitor 240 of FIG. 34 also includes an amplifier 725 to amplify and sense EEG signals from a cranially implanted lead 18. The CPU 732, in conjunction with a software program resident in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description as described below in association with FIG. 37.

FIG. 35 is a block diagram of the electronic circuitry that makes up external patch 160/full Monitor 260 with a brain lead 18 (FIG. 8) in accordance with the presently disclosed alternative embodiment of the invention. As can be seen from FIG. 35, Monitor 260 comprises a primary control circuit 720 and external patch comprises a cardiac/MV (minute ventilation) circuit 160, the functions of which have been described in detail above in conjunction with the system of FIG. 28. Intrinsic cardiac signals are sensed by electrodes affixed to the patient's skin, amplified by amplifier 724, sent to primary control circuit 720 and processed by CPU 732 and software program resident in RAM/ROM 730. Cardiac anomalies are detected such as heart rate variability, QT variability, QT_(C), sinus arrest, and various arrhythmias such as sinus, atrial and ventricular tachycardias. Respiration sensing is accomplished by low pass filtering the sensed and amplified intrinsic cardiac signals as shown in FIG. 27 or, alternatively, by using the MV/Z measurement circuitry of external patch 160 as described above in connection with FIG. 28. Respiration anomalies (such as reduced or cessation of tidal volume and apnea) are evaluated and detected by CPU 732 and software resident in RAM/ROM 730.

The CPU 732, in conjunction with a software program resident in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description as described below in association with FIG. 37.

The circuitry and function of the device 240 shown in FIG. 34 and described herein above may also be used for the full Monitor 280 with integrated electrode 24 brain lead 18 (FIG. 9). As described above in association with core Monitor 240, thoracic impedance via impedance/voltage converter as measured from the case of monitor 240 to the sensor stub 20 using a sampling frequency of approximately 16 Hz as substantially described in U.S. Pat. No. 4,596,251 “Minute Ventilation Dependant Rate Responsive Pacer” to Plicchi, et al. The Monitor 280 of this alternative embodiment utilizes the same circuitry of Monitor 240 but connected to the integrated electrode 24 on brain lead 18 instead of the sensor stub of Monitor 240.

Upon detection of either/or a cardiac or respiration anomaly, CPU 732, under control of firmware resident in RAM/ROM 730, will initiate recording of the appropriate diagnostic information into RAM of RAM/ROM 730, initiate a warning or alert to the patient, patient caregiver, or remote monitoring location. See flow diagram and description as described below in association with FIG. 37.

FIG. 36 is a block diagram of the electronic circuitry that makes up full Monitor 26 (FIG. 10) in accordance with the presently disclosed alternative embodiment of the invention. As can be seen from FIG. 32, Monitor 26 comprises a primary control circuit 720 whose function is described herein above in conjunction with FIG. 26. In addition the full Monitor 26 of FIG. 32 also includes an EEG amplifier 725 to amplify and sense EEG signals from a cranially implanted lead 18 or, alternatively, device mounted electrodes. Additionally, Sensor Interface 727 powers up, amplifies and senses the cardiac and respiratory signals from anyone or more of the following cranially implanted sensors. ECG sensing in the cranium may be accomplished by leadless ECG sensing as described in the above Brabec '940, Ceballos '915 and Lee '067 referenced patents. Alternatively, cardiac rate and asystole may be inferred from a dP/dt signal described above in the Anderson '813 patent; an acoustic signal described above in the Kieval '177 patent; an O₂sat signal described above in Moore '701 patent; a dT/dt signal described above in the Weijand '244 patent; a flow signal described above in the Olson '009; a strain gauge signal described above in the Bowman '759 patent; and a blood parameter sensor (such as oxygen, pulse or flow) located on a V-shaped lead described in the Taepke '318 patent.

The CPU 732, in conjunction with a software program resident in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description as described below in association with FIG. 37.

FIG. 37 is a flow diagram 840 showing operation of a full monitor sensing and monitoring cardiac, respiration and electroencephalogram parameters for the detection of neurological events as shown and described in embodiments in FIGS. 5-10 above. Beginning at block 802, the interval between sensed cardiac signals are measured. At block 804, a rate stability measurement is made on each cardiac interval utilizing a heart rate average from block 806. At block 808, a rate stable decision is made based upon preprogrammed parameters. If YES, the flow diagram returns to the HR Measurement block 802. If NO, the rate stability information is provided to Format Diagnostic Data block 812.

At block 816, thoracic impedance is continuously measured in a sampling operation. At block 818, a MV and respiration rate calculation is made. At block 822, a pulmonary apnea decision is made based upon preprogrammed criteria. If NO, the flow diagram returns to MV Measurement block 816. If YES, the occurrence of apnea and MV information is provided to Format Diagnostic Data block 812.

At block 824, the electroencephalogram is sensed and measured. An EEG seizure determination is performed at block 826 as described in US published application 2004/0138536 “Clustering of Recorded Patient Neurological Activity to Determine Length of a Neurological Event” to Frei, et al incorporated herein by reference. At block 828, a seizure cluster episode is determined. If NO, the flow diagram returns to EEG Measurement block 824. If YES, the occurrence of a seizure cluster is provided to Format Diagnostic Data block 812. Format Diagnostic Data block 812 formats the data from the cardiac, respiration and EEG monitoring channels, adds a time stamp (ie, date and time) and provides the data to block 814 where the data is stored in RAM memory for later retrieval by a clinician via telemetry. Optionally, block 812 may add examples of intrinsic ECG, respiration or EEG signals recorded during a sensed episode/seizure. Additionally, optionally, block 815 may initiate a warning or alert to the patient, patient caregiver, or remote monitoring location (as described in U.S. Pat. No. 5,752,976 “World Wide Patient Location and Data Telemetry System for Implantable Medical Devices” to Duffin, et al.

FIG. 38 is a diagram 850 of exemplary physiologic data from a patient 10 with a full monitor as described herein above showing an EEG signal 852 and an ECG signal 854. A first epileptic seizure is shown at 856 (pre-stimulation segment 851, stimulation segment 853 and post-stimulation segment 855) and detected at 864 and a second seizure is shown at 858 (pre-stimulation segment 857, stimulation segment 859 and post-stimulation segment 861) and detected at 866 by the full monitor. The ECG signal 854 shows a first arrhythmic episode at 860 and detected at 868 and a second arrhythmic episode at 862 and detected at 870 by the full monitor. Note that the first epileptic seizure 864 and arrhythmic episode 868 are co-incident and “matched”. Note that in the diagram 850 arrhythmic episode 870 and seizure episode 866 are not co-incident and are “unmatched”.

Segmenting a Cardiac Signal According to Brain Detection Results.

One embodiment of the inventive system provides an automated method of processing cardiac and/or respiratory signals in a full monitoring device (brain-heart, brain-respiratory or brain, heart and respiratory) for a nervous system disorder, to screen for cardiac abnormalities/heart rate changes and respiratory abnormalities during or within a specified time period of a neurological event. This embodiment medical device system and method may report a patient's heart or pulmonary condition for each neurological event detected in the brain signal.

In the case of epilepsy for example, changes in cardiac rate, presence of ECG abnormalities, and respiratory conditions (i.e., pulmonary edema) have been associated with seizures. Such changes in autonomic functioning have been postulated as important factors in epilepsy patients at risk of sudden death (SUDEP). The capability to monitor cardiac or respiratory function during seizures is important, as it allows for identification of co-existing autonomic conditions that may underlie SUDEP.

To determine changes in cardiovascular function that may arise from seizures, a method called stimulation-ECG segmentation has been developed for use in a medical device system. Upon detection of a brain event, as defined by a seizure-detection algorithm operating on EEG/ECoG signals, a corresponding portion of data in the ECG signal is identified. The identified portion of data may be further segmented into pre-stimulation, stimulation and post-stimulation portions. For each portion, heart rate metrics (mean, median, min, max, and standard deviation) may be calculated and ECG abnormalities (bradycardia, tachycardia, asystole, ST segment depression, QTc prolongation, etc.) may be identified. Measures of change between indices are then calculated by comparing the metrics.

Desirable features of such a seizure-heart rate monitoring system includes the ability to monitor the following: (1) HR levels (R-R intervals) associated with the time-course of the seizure, including pre-stimulation, stimulation, and post-stimulation periods; (2) HR changes associated with the onset and termination of the seizure; (3) time taken for heart rate to return to pre-stimulation levels (within specified range) following seizure termination; and (4) presence of ECG abnormalities associated with the seizure and timing of occurrence (before, during, or after stimulation period).

Such a system provides useful clinical information, in the form of an ECG seizure profile, for use in diagnosing and treating co-morbid cardiac conditions. For example, a physician would be able to determine the number and percentage of detected seizures for which there was an associated serious cardiac condition (e.g., tachycardia, asystolic pause, etc.), and be provided a detailed listing/summary of heart rate indices. Subsequent assessments could then determine whether the detected events necessitate cardiac treatment.

A seizure-heart rate monitoring system that employs stimulation ECG segmentation may also be used to help determine whether cardiac function is affected by the patient's seizure type. In some patients, large changes in heart rate or specific types of arrhythmias may be triggered with certain seizure types and/or their location of onset. Assessments for trend over time may be made by comparing ECG seizure metrics between detected neurological events. For example, by plotting and comparing % change in heart rate metrics over time.

In one embodiment, the medical device system includes a brain monitoring element, a cardiac monitoring element and one or more processors in communication with the brain monitoring element and the cardiac monitoring element and configured to perform a variety of operations. The various processing steps discussed may be performed within any hardware embodiment envisioned including but not limited to the various hardware embodiments presented throughout this application. For example, all of the processing steps may be performed within one or more implantable devices. Alternatively, some processing steps may be performed within one or more implantable devices and other processing steps performed by an external component of the system such as a programmer or computer that receives the appropriate information from the implanted device(s) by telemetry.

The one or more processors perform a number of operations. In one embodiment shown in FIG. 60, the one or more processors receive a brain signal at block 1102. The brain signal comes from the brain monitoring element. For example, the brain signal could be the output of an electrode that senses an EEG signal from the brain. The one or more processors determine at least one reference point for a brain event time period at block 1104. A brain event time period is the time period over which a neurological event is detected in the brain signal. In the epilepsy example, the brain event is a seizure and the brain event time period is the period of time identified by the detection or prediction algorithm as the seizure event. An appropriate algorithm determines the reference point of the neurological event based on the analysis of the brain signal. It is noted that some neurological events may have a more abrupt onset and offset while other neurological events may have a more gradual onset and offset. A reference point for a brain event time period may be any point in time that has some relationship to a detected event in the brain signal. For example, the reference point may be the starting point or ending point of a seizure according to a seizure detection algorithm evaluating the brain signal. Alternatively, the reference point could be the midpoint of a neurological event. Alternatively, the reference point could be a maximum point in the brain event (e.g., highest reading of whatever quantitative measure being used to evaluate the brain signal). Alternatively the reference point could be some point in time before seizure onset that is identified by the detection or prediction algorithm and that has some relationship to the brain event. The one or more processors receive a cardiac signal from the cardiac monitoring element at block 1106. The one or more processors then identify a first portion of the cardiac signal based on the at least one reference point at block 1108. Identifying a portion of a cardiac signal involves determining a beginning and an end of the portion. Some examples of a portion of the cardiac signal include pre-event portion, event portion and post-event portion. A pre-event portion is some portion that occurs before the starting point of a brain event time period. An event portion is a portion that occurs during a brain event time period. A post-event portion is a portion that occurs after the ending point of a brain event time period. In the example of epilepsy, the pre-event, event and post-event portions are referred to as the pre-stimulation, stimulation and post-stimulation portions respectively.

The flowchart at FIG. 61 illustrates an alternative embodiment of the operations performed by the one or more processors. At block 1202, the one or more processors receive a brain signal. An algorithm is performed by the one or more processors to determine at least one reference point (e.g., the starting point, the ending point or both) of the brain event time period at block 1204. Note that in the case of determining more than one reference point, the second reference point may be determined based on the first reference point. For example, if an algorithm detects the starting point of a neurological event, the algorithm may make an assumption that the ending point is a period of time after the starting point. Alternatively, both reference points may be determined by evaluation of the brain signal using a detection algorithm or other algorithm. The one or more processors receive a cardiac signal at block 1206. The one or more processors next identify two or more portions of the cardiac signal based on the starting and ending points of the brain event time period at block 1208. For example, one or more processors may identify a pre-event portion, event portion and post-event portion of the cardiac signal. Specifically in the case of epilepsy, the portions identified may be the pre-stimulation, stimulation and post-stimulation portions of the cardiac signal. The identification of portions of the cardiac signal based on starting and ending points of the brain event time period may be by a simple relationship between the starting and ending points and the portions or it may be complex. Some examples of ways to identify portions of the cardiac signal are provided. In one embodiment illustrated in FIG. 62, identification of a pre-stimulation portion of the cardiac signal involves identifying the portion of the cardiac signal between a programmable first period of time before the starting point to the starting point. The post-stimulation portion of the cardiac signal may be identified as the portion of the cardiac signal between the ending point of the brain event time period and a third period of time after the ending point. Another exemplary embodiment method of identifying portions of a cardiac signal is illustrated in FIG. 63. Here, the pre-stimulation portion is identified as the portion between a first period of time before the starting point to a second period of time before the starting point. Furthermore, the post-stimulation portion is identified as the portion between a fourth period of time after the ending point to a third period of time after the ending point. In one embodiment, the time periods may be programmable. In another embodiment, they may be fixed.

The process may start with analysis of the brain signal. The terms “starting point” and “ending point” include points in time determined by an algorithm that may not necessarily correlate with a sharp or distinct change in the brain signal. For example a slight increase in features indicative of major depressive disorder may be sufficient for the algorithm to make the determination of a starting point even though a distinct or abrupt change in the brain signal is not observed. In the case of epilepsy a seizure detection algorithm may be used some of which have been cited elsewhere in this application. In the case of psychiatric disorders such as depression, a psychiatric monitoring algorithm may be used. For example, EEG asymmetry across different hemispheres of the brain may be evaluated to detect a depression event. One exemplary algorithm that may be used for depression is described in U.S. Published Patent Application 2005/0216071. The methods described in U.S. Pat. No 6,622,036 may also be used.

Once one or more portions of the cardiac signal are identified, they may be stored in memory at block 1210. The phrase “stored in memory” means keeping the information so that it can be analyzed. For example, the phrase “stored in memory” includes retaining (rather than discarding) information in a circular buffer such as in a loop recording scheme. In one embodiment monitoring device for epilepsy, brain signals are monitored/processed with a seizure detection algorithm; the cardiac and respiratory signals are passively recorded during the brain signal processing. When a seizure has been detected in the brain signal data stream, a recording containing a montage of brain, cardiac and respiratory signals is created. The signals in the recording are then processed to evaluate the patient's heart and pulmonary condition.

At block 1212, the one or more processors may determine metrics of one or more of the pre-event, event and post-event portions of the cardiac signal. In one embodiment, the metrics may relate to heart rate. Some of the heart rate metrics that may be determined include the following that may be taken over the entire portion of the cardiac signal or over a subset of the portion: mean heart rate, median heart rate, maximum heart rate, minimum heart rate and standard deviation of the heart rate.

Once metrics are determined they may be compared at block 1214. Comparison of metrics means any comparison between two metrics. For example, percentage change from one metric to a second metric may be computed. In one embodiment, the pre-event metric may be compared to the post-event metric. In one embodiment the post-event portion may be divided into sub-portions, metrics computed for the sub-portions, and the sub-portion metrics compared to the pre-event metric. This may be done to determine how long it takes the patient's heart rate to return to normal after a brain event such as a seizure. In another embodiment, the pre-event metric may be compared to the event metric. In yet another embodiment, the event metric may be compared to the post-event metric.

In one embodiment, it may be desirable to have a processor in the implantable medical device portion of the system identify the portions of the cardiac signal (e.g., pre-stimulation, stimulation, post-stimulation) and to store them, and to have a second processor in a programmer or other external device receive the portions of cardiac signal via telemetry and determine metrics and compare metrics. In yet another embodiment, the implanted processor may determine the metrics associated with the portions and send only the metrics to the external device via telemetry. The external device may then evaluate or compare the metrics. In yet another embodiment, the brain and cardiac signals may be telemetered to the external device and post-processed by the external device to identify the portions, determine the metrics and compare the metrics.

FIG. 39 shows one embodiment process 750 for identifying ECG and respiratory abnormalities recorded during detected seizures. At block 751, the full monitor monitors EEG and ECG or respiratory signals. At block 752, the monitor detects seizures in EEG signals. At block 753, seizure detection triggers recording and retention of EEG, ECG and respiratory signals. After uplinking to a programmer, the ECG/respiratory signals are post-processed. At this point one or more processors may identify an event portion, pre-event portion and post-event portion of the cardiac signal based on the starting point and the ending point of the brain event time period. The event portion of the cardiac signal may correspond in time exactly to the brain event time period such as an stimulation period, or it may be different but computed based on the starting and ending points of the brain event time period. The pre-event portion of the cardiac signal may be everything before the event time period or it may be a period beginning a programmable period of time before the event time period to the beginning of the event time period. Likewise, the post-event time period may be everything after an event time period or it may be a period beginning at the end of the event time period and extending to a programmable period of time after the end of the event time period. For the seizure example, at block 755, ECG and respiratory signals are segmented into (a) pre-stimulation, (b) stimulation, and (c) post-stimulation periods based upon the determined starting and ending points of the neurological event in the brain signal. The stimulation periods are automatically derived from a seizure-detection algorithm operating on the EEG signals. For example, the beginning of the stimulation period may be time-marked to detection cluster onset; the end of the stimulation period by detection cluster offset (as described in published US Application No. 2004/0138536 “Clustering of Recorded Patient Neurological Activity to Determine Length of a Neurological Event” to Frei, et al incorporated herein by reference in its entirety). The durations of the pre-stimulation and post-stimulation periods are programmable. It may be desirable to program the pre-stimulation period for purposes of a cardiac baseline or respiratory baseline as ending some period of time before or after the true stimulation period as determined by the EEG detector. In this way a better baseline may be obtained that is not distorted by changes in cardiac or respiratory activity near in time to the neurological event.

At block 756, the loop-recorded data is screened for abnormalities. After the ECG and respiratory signals are segmented, the different intervals of ECG and respiratory data are separately processed to determine metrics associated with those signals. The term metric is used interchangeably herein with the term indices. These metrics may assist in detecting events or determining features or other activity reflected in those signals. Exemplary cardiac metrics that may be computed include indices of heart rate (HR) (i.e., mean, median, max, std. dev., etc.) or indications of abnormal heart activity such as an arrhythmia which are displayed in the physician programmer for each detected event. Exemplary respiratory metrics that may be computed include minute ventilation, respiration rate, apnea, or edema, which are displayed in the physician programmer for each detected event. Metrics from different segmented intervals or time periods of the cardiac or respiratory signal may be compared to one another. For example, to monitor changes in cardiovascular and pulmonary function that may arise from or cause seizures, percentage of change between indices/metrics may be calculated. For example, to indicate magnitude of change in heart rate from a baseline to seizure state, the percentage of change between the pre-stimulation (baseline) and stimulation (seizure) periods is computed/displayed.

% Chg. Detect Onset=(Stimulation HR indice-Base HR indices)/Base HR indices

Comparison between the post-stimulation and baseline periods is also performed to evaluate if and when a return to baseline is achieved.

% Chg. Detect End=(Post-Stimulation HR indices-Base HR indices)/Base HR indices

During processing, the time at which the post-stimulation heart rate returns to baseline, relative to the end of the stimulation period, is identified. The physician may choose to increase the duration of the post-stimulation period if, during detected seizures, the patient's HR indices do not consistently return to baseline levels.

At block 757, detection times for arrhythmic and respiratory anomalies are determined. The ECG and respiratory signals are further processed, via an arrhythmia/abnormality detection algorithm, to identify ECG and respiratory abnormalities (bradycardia, tachycardia, asystole, ST segment depression, QTc prolongation, apnea, edema, etc.). Such events may occur in different periods of data, and cross stimulation boundaries (e.g., a tachy event may begin prior to seizure onset, and continue well after seizure termination, resulting in a detection that includes all intervals of data). Thus, during screening the entire ECG and respiration signals in the loop recording data is processed in a single step, without segmentation. The start and end times for each identified arrhythmia/abnormality in the loop recording data is stored and later retrieved for analysis.

The physician may further run a matching test (EEG detections versus ECG or respiratory detections) at block 758. The matching test is run to compare the EEG detections and ECG/respiratory detections in the loop recording data. The matching test reports whether each ECG/respiratory abnormality is coincident with (i.e., matched), or is temporally separated from, the detected seizure (i.e., unmatched). In the case of a match, the time difference between EEG detection onset and ECG/respiratory detection onset is computed.

At block 759, the matching test results are evaluated to determine if the seizure is associated with an arrhythmia or respiratory anomaly. At block 760, additional seizures are determined. If NO, block 761 reports results of ECG/respiratory screening procedures for each seizure. At block 760, if the result is YES the flow diagram returns to block 752.

ECG/respiratory post-processing may occur in the implantable device, after the loop recorded data has been stored to memory. Alternatively, the post-processing may occur on loop-recorded data transmitted to an external wearable device or physician programmer or other computer.

In another embodiment of cardiac signal segmentation it may be desirable to record the amount of time it takes a metric of the cardiac signal to return to some baseline metric after a change in the brain signal has been discovered. For example, the system may determine a first metric such as heart rate associated with a pre-event portion of the cardiac signal. The first metric is the baseline. The system then determines a second metric for the post-event portion and determines whether it meets predetermined criteria about its relationship to the first metric. The predetermined criteria may be any way of determining or estimating whether the second metric (e.g., heart rate after the seizure) has reached or is close enough to the first metric (e.g., the heart rate before the seizure). For example, the predetermined criteria may simply be to determine whether the second metric equals the first metric. Another example of predetermined criteria may be a determination of whether the second metric is within a specified range of the first metric. In another exemplary embodiment, the predetermined criteria may evaluate whether successive metrics cross from being greater than the first metric to less than the first metric or vice versa. Once the value of the first metric is crossed the predetermined criteria are met. If the predetermined criteria are met, a second metric time is recorded or otherwise transmitted. The second metric time means some time value related to the amount of time from the at least one reference point to the occurrence of the second portion. For example, in one embodiment, the second metric time is the amount of time from the ending point of the seizure to the point in time when the heart rate has returned to its pre-stimulation level. In this way the clinician may learn for each event the amount of time it took a particular metric of the patient's cardiac signal to return to baseline. In one embodiment the second portion may be a short or very short period of time such as, for example, 10 seconds, 5 seconds, 2 seconds, 1 second, or less than 1 second, or even on a sample by sample basis (e.g., determine a new metric each time there is a heart beat). By using a short second portion, successive portions may be evaluated until the metric associated with the portions meets the predetermined criteria.

Segmenting a Cardiac Signal According to Brain Stimulation Results.

One embodiment of the inventive system provides an automated method of processing cardiac and/or respiratory signals in a full monitoring device (brain-heart, brain-respiratory or brain, heart and respiratory) for a nervous system disorder, to screen for cardiac abnormalities/heart rate changes and respiratory abnormalities during or within a specified time period of a brain stimulation event. This embodiment medical device system and method may report a patient's heart or pulmonary condition for each delivered stimulation event.

Changes in cardiac rate, presence of ECG abnormalities, and respiratory function can be affected with electrical brain stimulation. During programming of deep brain stimulation (DBS) devices, stimulation parameters are selected to avoid or minimize these effects from occurring during continuous, open-loop, or closed-loop stimulation therapy. Thus, the capability to monitor cardiac or respiratory function during brain stimulation is important.

To determine changes in cardiovascular function that may arise from brain stimulation, a method called brain stimulation ECG segmentation has been developed for use in a medical device system. Upon delivery of brain stimulation to a patient, a corresponding portion of data in the ECG signal is identified. The identified portion of data may be further segmented into pre-stimulation, stimulation and post-stimulation portions. For each portion, heart rate metrics (mean, median, min, max, and standard deviation) may be calculated and ECG abnormalities (bradycardia, tachycardia, asystole, ST segment depression, QTc prolongation, etc.) may be identified. Measures of change between indices are then calculated by comparing the metrics.

Desirable features of such a brain stimulation-heart rate monitoring system includes the ability to monitor the following: (1) HR levels (R-R intervals) associated with the time-course of the brain stimulation, including pre-stimulation, stimulation, and post-stimulation periods; (2) HR changes associated with the onset and termination of the brain stimulation; (3) time taken for heart rate to return to pre-stimulation levels (within specified range) following brain stimulation termination; and (4) presence of ECG abnormalities associated with the brain stimulation and timing of occurrence (before, during, or after stimulation period).

Such a system provides useful clinical information, in the form of an ECG stimulation profile, for use in evaluating the effects of brain stimulation on cardiac function. For example, a physician would be able to determine the number and percentage of delivered brain stimulations for which there was an associated cardiac change (e.g., tachycardia, asystolic pause, etc.), and be provided a detailed listing/summary of heart rate indices. Subsequent assessments could then determine which delivered brain stimulations had affected cardiac function.

A brain stimulation-heart rate monitoring system that employs stimulation ECG segmentation may also be used to help determine whether cardiac function is affected by the type of brain stimulation delivered—this includes the duration, intensity, pulse width, pulse shape, electrode contact configuration, electrode polarities, and type of stimulation signal (voltage or constant current). With some DBS targets, changes in heart rate or specific types of arrhythmias may be triggered with certain brain stimulation parameter settings. Assessments for trend over time may be made by comparing ECG stimulation metrics between delivered stimulation events. For example, by plotting and comparing % change in heart rate metrics over time.

In one embodiment, the medical device system includes a brain stimulating element, a cardiac monitoring element and one or more processors in communication with the brain stimulating element and the cardiac monitoring element and configured to perform a variety of operations. The various processing steps discussed may be performed within any hardware embodiment envisioned including but not limited to the various hardware embodiments presented throughout this application. For example, all of the processing steps may be performed within one or more implantable devices. Alternatively, some processing steps may be performed within one or more implantable devices and other processing steps performed by an external component of the system such as a programmer or computer that receives the appropriate information from the implanted device(s) by telemetry.

The one or more processors perform a number of operations. In one embodiment shown in FIG. 64, the one or more processors receive a brain stimulation signal at block 2102. The brain stimulation signal comes from the brain stimulating element. For example, the brain stimulation signal could be the output of an electrode that delivers a stimulation signal to the brain. The brain stimulation signal may be either a continuous signal (e.g., voltage or current×time), or a binary signal that represents the stimulation state (i.e., when stimulation has been toggled on or off). Alternatively, a stimulation event log may be used in place of, and to represent, the stimulation signal. The one or more processors determine at least one reference point for a brain stimulation event time period at block 2104. A brain stimulation event time period is the time period over which a stimulation event is delivered to the brain.

An appropriate algorithm determines the reference point of the stimulation event based on the analysis of brain stimulation signal or event log. It is noted that some brain stimulation events may have a more abrupt onset and offset while other brain stimulation events may have a more gradual onset and offset, such as with soft-start therapy modes. A reference point for a brain stimulation event time period may be any point in time, and depending on the therapy delivery mode, may or may not have some relationship to a detected event in the brain signal. For example, the reference point may be the starting point or ending point of the brain stimulation event. Alternatively, the reference point could be the midpoint of a brain stimulation event. Alternatively, the reference point could be a maximum point in the brain stimulation event. Alternatively the reference point could be some point in time before brain stimulation event onset.

The one or more processors receive a cardiac signal from the cardiac monitoring element at block 2106. The one or more processors then identify a first portion of the cardiac signal based on the at least one reference point at block 2108. Identifying a portion of a cardiac signal involves determining a beginning and an end of the portion. Some examples of a portion of the cardiac signal include pre-event portion, event portion and post-event portion. A pre-event portion is some portion that occurs before the starting point of a brain stimulation event time period. An event portion is a portion that occurs during a brain stimulation event time period. A post-event portion is a portion that occurs after the ending point of a brain stimulation event time period.

The flowchart at FIG. 65 illustrates an alternative embodiment of the operations performed by the one or more processors. At block 2202, the one or more processors receive a brain stimulation signal. An algorithm is performed by the one or more processors to determine at least one reference point (e.g., the starting point, the ending point or both) of the brain stimulation event time period at block 2204. Note that in the case of determining more than one reference point, the second reference point may be determined based on the first reference point. For example, if an algorithm detects the starting point of a stimulation event, the algorithm may make an assumption that the ending point is a period of time after the starting point. Alternatively, both reference points may be determined by evaluation of the brain stimulation signal using a detection algorithm or other algorithm. The one or more processors receive a cardiac signal at block 2206. The one or more processors next identify two or more portions of the cardiac signal based on the starting and ending points of the brain stimulation event time period at block 2208. For example, one or more processors may identify a pre-event portion, event portion and post-event portion of the cardiac signal. Specifically in the case of stimulation, the portions identified may be the pre-stimulation, stimulation and post-stimulation portions of the cardiac signal. The identification of portions of the cardiac signal based on starting and ending points of the brain stimulation event time period may be made by a simple relationship between the starting and ending points and the portions or it may be complex. Some examples of ways to identify portions of the cardiac signal are provided. In one embodiment illustrated in FIG. 66, identification of a pre-stimulation portion of the cardiac signal involves identifying the portion of the cardiac signal between a programmable first period of time before the starting point to the starting point. The post-stimulation portion of the cardiac signal may be identified as the portion of the cardiac signal between the ending point of the brain stimulation event time period and a third period of time after the ending point. Another exemplary embodiment method of identifying portions of a cardiac signal is illustrated in FIG. 67. Here, the pre-stimulation portion is identified as the portion between a first period of time before the starting point to a second period of time before the starting point. Furthermore, the post-stimulation portion is identified as the portion between a fourth period of time after the ending point to a third period of time after the ending point. In one embodiment, the time periods may be programmable. In another embodiment, they may be fixed.

The process may start with analysis of the brain stimulation signal. Once one or more portions of the cardiac signal are identified, they may be stored in memory at block 2210. The phrase “stored in memory” means keeping the information so that it can be analyzed. For example, the phrase “stored in memory” includes retaining (rather than discarding) information in a circular buffer such as in a loop recording scheme. In one embodiment stimulating device for epilepsy, brain stimulation signals are monitored/processed with a stimulation detection algorithm; the cardiac and respiratory signals are passively recorded during the brain stimulation signal processing. When a stimulation signal has been detected, a recording containing a montage of brain, cardiac and respiratory signals is created. The signals in the recording are then processed to evaluate the patient's heart and pulmonary condition.

At block 2212, the one or more processors may determine metrics of one or more of the pre-event, event and post-event portions of the cardiac signal. In one embodiment, the metrics may relate to heart rate. Some of the heart rate metrics that may be determined include the following that may be taken over the entire portion of the cardiac signal or over a subset of the portion: mean heart rate, median heart rate, maximum heart rate, minimum heart rate and standard deviation of the heart rate.

Once metrics are determined they may be compared at block 2214. Comparison of metrics means any comparison between two metrics. For example, percentage change from one metric to a second metric may be computed. In one embodiment, the pre-event metric may be compared to the post-event metric. In one embodiment the post-event portion may be divided into sub-portions, metrics computed for the sub-portions, and the sub-portion metrics compared to the pre-event metric. This may be done to determine how long it takes the patient's heart rate to return to normal after a brain stimulation event. In another embodiment, the pre-event metric may be compared to the event metric. In yet another embodiment, the event metric may be compared to the post-event metric.

In one embodiment, it may be desirable to have a processor in the implantable medical device portion of the system identify the portions of the cardiac signal (e.g., pre-stimulation, stimulation, post-stimulation) and to store them, and to have a second processor in a programmer or other external device receive the portions of cardiac signal via telemetry and determine metrics and compare metrics. In yet another embodiment, the implanted processor may determine the metrics associated with the portions and send only the metrics to the external device via telemetry. The external device may then evaluate or compare the metrics. In yet another embodiment, the brain stimulation and cardiac signals may be telemetered to the external device and post-processed by the external device to identify the portions, determine the metrics and compare the metrics.

FIG. 68 shows one embodiment process 1750 for identifying ECG and respiratory abnormalities recorded during delivered stimulations. At block 1751, the full monitor monitors EEG and ECG or respiratory signals. At block 1752, the processor delivers electrical stimulation to the brain of the patient. The stimulation may be delivered during the test trials of therapy or it may be delivered during open or closed loop therapy. At block 1753, stimulation delivery triggers recording and retention of EEG, ECG and respiratory signals. After uplinking to a programmer, the ECG/respiratory signals are post-processed. At this point one or more processors may identify an event portion, pre-event portion and post-event portion of the cardiac signal based on the starting point and the ending point of the brain stimulation event time period. The event portion of the cardiac signal may correspond in time exactly to the brain stimulation event time period, or it may be different but computed based on the starting and ending points of the brain stimulation event time period. The pre-event portion of the cardiac signal may be everything before the event time period or it may be a period beginning a programmable period of time before the event time period to the beginning of the event time period. Likewise, the post-event time period may be everything after an event time period or it may be a period beginning at the end of the event time period and extending to a programmable period of time after the end of the event time period. For the stimulation example, at block 1755, ECG and respiratory signals are segmented into (a) pre-stimulation, (b) stimulation, and (c) post-stimulation periods based upon the determined starting and ending points of the brain stimulation signal. The stimulation periods are automatically derived from processing of the corresponding brain stimulation signal, or alternatively, a stimulation log containing the stimulation event times. The durations of the pre-stimulation and post-stimulation periods are programmable. It may be desirable to program the pre-stimulation period for purposes of a cardiac baseline or respiratory baseline as ending some period of time before or after the true stimulation period. In this way a better baseline may be obtained that is not distorted by changes in cardiac or respiratory activity near in time to the stimulation event.

At block 1756, the loop-recorded data is screened for abnormalities. After the ECG and respiratory signals are segmented, the different intervals of ECG and respiratory data are separately processed to determine metrics associated with those signals. The term metric is used interchangeably herein with the term indices. These metrics may assist in detecting events or determining features or other activity reflected in those signals. Exemplary cardiac metrics that may be computed include indices of heart rate (HR) (i.e., mean, median, max, std. dev., etc.) or indications of abnormal heart activity such as an arrhythmia which are displayed in the physician programmer for each brain stimulation event. Exemplary respiratory metrics that may be computed include minute ventilation, respiration rate, apnea, or edema, which are displayed in the physician programmer for each brain stimulation event. Metrics from different segmented intervals or time periods of the cardiac or respiratory signal may be compared to one another. For example, to monitor changes in cardiovascular and pulmonary function that may arise from brain stimulation, percentage of change between indices/metrics may be calculated. For example, to indicate magnitude of change in heart rate from a baseline to stimulation state, the percentage of change between the pre-stimulation (baseline) and stimulation periods is computed/displayed.

% Chg. Detect Onset=(Stimulation HR indices-Base HR indices)/Base HR indices

Comparison between the post-stimulation and baseline periods is also performed to evaluate if and when a return to baseline is achieved.

% Chg. Detect End=(Post-Stimulation HR indices-Base HR indices)/Base HR indices

During processing, the time at which the post-stimulating heart rate returns to baseline, relative to the end of the stimulation period, is identified. The physician may choose to increase the duration of the post-stimulation period if, during delivered stimulation, the patient's HR indices do not consistently return to baseline levels.

At block 1757, detection times for arrhythmic and respiratory anomalies are determined. The ECG and respiratory signals are further processed, via an arrhythmia/abnormality detection algorithm, to identify ECG and respiratory abnormalities (bradycardia, tachycardia, asystole, ST segment depression, QTc prolongation, apnea, edema, etc.). Such events may occur in different periods of data, and cross stimulation boundaries (e.g., a tachy event may begin prior to stimulation, and continue well after stimulation termination, resulting in a detection that includes all intervals of data). Thus, during screening the entire ECG and respiration signals in the loop recording data is processed in a single step, without segmentation. The start and end times for each identified arrhythmia/abnormality in the loop recording data is stored and later retrieved for analysis.

The physician may further run a matching test (brain stimulations versus ECG or respiratory detections) at block 1758. The matching test is run to compare the brain stimulation signals and ECG/respiratory detections in the loop recording data. The matching test reports whether each ECG/respiratory abnormality is coincident with (i.e., matched), or is temporally separated from, the delivered brain stimulation signal (i.e., unmatched). In the case of a match, the time difference between brains stimulation signal and ECG/respiratory detection onset is computed.

At block 1759, the matching test results are evaluated to determine if the brain stimulation event is associated with an arrhythmia or respiratory anomaly. At block 1760, the results of the ECG/respiratory screening procedures for brain stimulation event(s) are logged and/or reported.

ECG/respiratory post-processing may occur in the implantable device, after the loop recorded data has been stored to memory. Alternatively, the post-processing may occur on loop-recorded data transmitted to an external wearable device or physician programmer or other computer.

In another embodiment of cardiac signal segmentation it may be desirable to record the amount of time it takes a metric of the cardiac signal to return to some baseline metric after a change in the brain stimulation signal has been detected. For example, the system may determine a first metric such as heart rate associated with a pre-event portion of the cardiac signal. The first metric is the baseline. The system then determines a second metric for the post-event portion and determines whether it meets predetermined criteria about its relationship to the first metric. The predetermined criteria may be any way of determining or estimating whether the second metric (e.g., heart rate after the seizure) has reached or is close enough to the first metric (e.g., the heart rate before the stimulation event). For example, the predetermined criteria may simply be to determine whether the second metric equals the first metric. Another example of predetermined criteria may be a determination of whether the second metric is within a specified range of the first metric. In another exemplary embodiment, the predetermined criteria may evaluate whether successive metrics cross from being greater than the first metric to less than the first metric or vice versa. Once the value of the first metric is crossed the predetermined criteria are met. If the predetermined criteria are met, a second metric time is recorded or otherwise transmitted. The second metric time means some time value related to the amount of time from the at least one reference point to the occurrence of the second portion. For example, in one embodiment, the second metric time is the amount of time from the ending point of the stimulation event to the point in time when the heart rate has returned to its pre-stimulation level. In this way the clinician may learn for each event the amount of time it took a particular metric of the patient's cardiac signal to return to baseline. In one embodiment the second portion may be a short or very short period of time such as, for example, 10 seconds, 5 seconds, 2 seconds, 1 second, or less than 1 second, or even on a sample by sample basis (e.g., determine a new metric each time there is a heart beat). By using a short second portion, successive portions may be evaluated until the metric associated with the portions meets the predetermined criteria.

Determination of Improvements in Neuroligical Event Detection using Cardiac or Respiratory Input

Another embodiment of the invention is a medical device system and method for determining whether cardiac or respiratory signals may be used to improve neurological event detection. This medical device system includes a brain monitoring element (e.g., lead 18, external electrode), a cardiac monitoring element (e.g., lead 16, sensor stub 20, sensor 14, integrated electrode 24, external electrode, etc.) or respiratory monitoring element (e.g., lead 16, sensor stub 20, sensor 14, integrated electrode 24, external electrode, etc.) and a processor (e.g., CPU 732 or any other processor or combination of processors implanted or external). This determination of whether cardiac or respiratory signals may be used to improve neurological event detection may be very beneficial to understanding a patient's condition and that in turn is helpful to determining appropriate treatment or prevention options. The medical device system may include the ability to determine relationships between brain and heart only, brain and respiratory only, or both. Once these relationships are better understood, they may be utilized to make decisions about enabling the use of cardiac signals or cardiac detections or respiratory signals or respiratory detections in the monitoring or treatment of the neurological disorder. Note that this medical device system and method may be performed by many different types of hardware embodiments including the example hardware embodiments provided in this specification as well as in an external computer or programmer. The executable instructions executed by a processor may be stored in any computer readable medium such as, for example only, RAM 730.

The determination of improvements in neurological event detection using cardiac or respiratory input includes determination of concordance between brain and cardiac signals or between brain and respiratory signals, determination of detection latency, and the false positive rate in the cardiac or respiratory signal relative to a neurological event detected in the brain signal.

An example of the usefulness of this determination is provided here. If it is determined that a patient with epilepsy has improvement in neurological event detection based on a cardiac signal it may be desirable to enable the use of a cardiac activity detection algorithm to trigger application of therapy to the brain. Another example of the benefit of concordance information is that a high concordance between brain and heart (including perhaps concordance with a particular type of cardiac event) for an individual with epilepsy, may mean that the patient is more susceptible to SUDEP. Perhaps steps can be taken such as use or implantation of a heart assist device such as a pacemaker or defibrillator for this patient to reduce the likelihood of death. There are of course many other examples of situations that may be discovered by operation of this concordance system and method that result in better health care.

The medical device system with concordance capability may include a brain monitoring element 18 (e.g., EEG lead with one or more electrodes) for sensing activity of the brain and outputting a brain signal, and a cardiac or respiratory monitoring element 14 (e.g., electrodes or other sensors) or both, for sensing a cardiac or respiratory activity and outputting a cardiac or respiratory signal, and a processor. The processor is configured to receive the brain signal and one or more of the cardiac and respiratory signals and to compare the brain signal and one of the cardiac or respiratory signals to each other.

Comparison of the brain and cardiac signals to each other may take many different forms. In one embodiment, the processor is configured to obtain information identifying one or more neurological events in the brain signal, and to also obtain information identifying one or more cardiac events in the cardiac signal. “Obtain” means 1) automatically generating the information by executing an algorithm that evaluates the signal, or 2) receiving the information from a user such as a physician reviewing the brain and cardiac signals (this second aspect of obtain is hereinafter referred to as “manual identification of events”). The algorithm or physician may create or generate various features of the neurological event such as a determination of when the event begins and ends and hence a duration of the event. For example automatic generation of the information may be performed by a seizure detection algorithm such as described in US published application 2004/0138536 “Clustering of Recorded Patient Neurological Activity to Determine Length of a Neurological Event” to Frei, et al. Likewise in the case of a cardiac signal, any algorithm that evaluates a cardiac signal and outputs information about cardiac activity or abnormalities would be an automatic generation of the information. Some examples are presented above in the discussion of the core monitor. An example of a manual identification of an event includes a physician indicating to a physician programmer the temporal location of a neurological event and also indicating the temporal location of cardiac or respiratory events. This temporal location of an event may include marking of the beginning and end of the event.

In the case of manual identification of an event, the medical device system may include a user interface (for example, on a programmer or computer), for display of the brain, cardiac and respiration signals. The user, such as a physician, may mark events on the programmer. For example, the physician could mark the location by clicking a cursor over the location on the monitor. In another example, the physician could mark a location with a stylus on a touch sensitive screen. The physician markings may include marks that indicate the beginning and the end of an event.

In a more specific embodiment, the comparison of the brain signal to the cardiac or respiration signal includes for each neurological event, determining whether the neurological event is within a specified time period of one of the one or more cardiac or respiratory events, and for each of the one or more cardiac or respiratory events determining whether the cardiac or respiratory event is within a specified time period of one of the one or more neurological events. Two events are “within a specified time period” of each other if the two events are overlapping in time or the amount of time between two reference points of the two events is less than a time period that is previously determined and set in the device or that has been programmed or may be programmed into the device. Reference points of an event are some measure or indication of the temporal position of the event. For example, the two reference points may be the end of the first of the events to end and the beginning of the other event. Other reference points may be used such as, but not limited to, the midpoints of each of the events. An example of a specified time period that could be programmed into the device is 10 seconds. So in this example, the neurological event and the cardiac event would be within the specified time period of each other if a chosen reference point for the cardiac event (e.g., end of the cardiac event) was within 10 seconds of a chosen reference point (e.g., beginning of the neurological event) for the neurological event.

The comparison of brain signal to cardiac signal may include the following: determining the number of neurological events that are matched with a cardiac event (i.e., within a specified time period of a cardiac event); determining the number of neurological events that are matched with a cardiac event (i.e., not within the specified time period of a cardiac event); and determining the number of cardiac events that are not within the specified time period of a neurological event (the false positive rate in the ECG signal). The same steps may be applied in the case of comparison of a brain signal to a respiratory signal.

Furthermore for matched events (events that are within the specified time period of each other), the processor may determine the temporal relationship of the neurological event and the matched cardiac event or between the neurological event and the matched respiratory event. Because matched events may overlap or they may not overlap, the temporal relationship may be defined or described in many different ways. One embodiment of determining the temporal relationship is determining the temporal order (which event is first to occur) of the matched events. In order to determine the temporal order between two events, a reference point must be determined. As mentioned earlier the reference point may be the end, start or midpoint of an event, or the reference point may be computed in some other way. In general a reference point indicates some temporal information about the event. The reference points may then be compared to determine which occurred first. The event associated with the first to occur reference point is then the first to occur event.

In another embodiment of comparing the brain signal to a cardiac or respiratory signal, the processor is configured to compute a rate of concordance between the neurological events and the cardiac or respiratory events. In this embodiment, the processor is configured to categorize the neurological event as cardiac matched when there is a cardiac event within a specified time period of the neurological event. The processor computes the rate of concordance between the neurological events and the cardiac events based on the number of cardiac matched events and the number of neurological events. For example, the processor may compute the rate of concordance by calculating the number of cardiac matched events divided by the number of neurological events. The more matches the greater the concordance.

In another embodiment the processor is further configured to perform the following: dividing the neurological event into at least two segments (portions); and assigning the cardiac event to one or more of the segments according to when the cardiac event occurred relative to the segments. For example, if the neurological event is a seizure, then there may be three segments: a pre-stimulation segment, an stimulation segment, and a post stimulation segment. Various methods may be used to assign a cardiac event to one of these segments. For example, an algorithm executed by the processor (e.g., any of the processors of the many hardware embodiments in this application such as CPU 732, or a processor in a programmer or other computer external to the body) may determine when the cardiac event started relative to the three segments and assign the cardiac event to the segment in which it started. Of course other methods, more complex or simple may be used to make this assignment.

The ECG algorithm may be automatically enabled/disabled for use in monitoring or treatment (as described herein below) if concordance, detection latency and false positive rates meet selected and programmable criteria, indicating an improvement in neurological event detection performance. Alternatively, the patient's clinician may choose to review matching results and manually enable/disable the ECG detector based on information provided. For example, detection of a cardiac event may result in turning a neurostimulator or drug delivery device on to prevent the onset of a seizure. Alternatively, detection of a cardiac event may result in modification of therapy parameters. In another alternative, the ECG detector may be enabled for purposes of recording ECG, EEG or some other data.

In the embodiment that includes therapeutic output, the medical device system further includes a neurological therapy delivery module configured to provide a therapeutic output to treat a neurological disorder when the cardiac event detection algorithm detects a cardiac event. A neurological therapy delivery module may be any module capable of delivery a therapy to the patient to treat a neurological disorder. For example, but not limited to, a neurological therapy delivery module may be an electrical stimulator (e.g., stimulator 729), drug delivery device, therapeutic patch, brain cooling module.

Depending on the individual patient, and depending on the particular neurological disorder of concern, there may be different levels of concordance between different types of cardiac events and the neurological events. Therefore, in another embodiment, the processor is further configured to obtain information categorizing each cardiac event as one or more of two or more types of cardiac events. Types of cardiac events are known by different signals or aspects of signals coming from the heart. Examples of different types of cardiac events include: tachyrhythmia, ST segment elevation, bradycardia, asystole. In this embodiment, the processor may then determine concordance between each type of cardiac event or subset of cardiac events and neurological events. One embodiment of such determination is a processor configured to categorize each neurological event as first type cardiac matched when there is a first type cardiac event within a specified time period of the neurological event. The processor further categorizes the neurological event as second type cardiac matched when there is a second type cardiac event within a specified time period of the neurological event. The processor further computes a first rate of concordance between the neurological events and the first type cardiac events based on the number of first type cardiac matched events and the number of neurological events. The processor also computes a second rate of concordance between the neurological events and the second type cardiac events based on the number of second type cardiac matched events and the number of neurological events. This computation of rate of concordance may be performed as many times as there are types of cardiac events. The categorization of events as well as the various computed rates of concordance may be stored in memory.

In the embodiment allowing for computation of specific type of cardiac event rates of concordance, the medical device system may further include the capability to enable the use of detection of a particular type of cardiac event to affect the provision of therapy to the patient for the neurological disorder. For example, if it is determined that a high rate of concordance exists between tachyarrhythmia and seizure, the enablement of cardiac detection for affecting seizure therapy may be limited to the detection of tachyarrythmia. In this case the seizure therapy will not be affected by other types of cardiac events.

It is noted that the medical device system may be external to the patient's body, implanted or some combination. The processor itself may be either external or implanted. For example, the processor may be in a handheld unit such as a programmer, or the processor could be in a general purpose computer.

The various processor operations described above may be embodied in executable instructions and stored in a computer readable medium. The processor then operates to perform the various steps via execution of these instructions. At one level, the executable instructions cause the processor to receive a brain signal from a brain monitoring element, receive a cardiac signal from a hear monitoring element, and compare the brain signal to the cardiac signal.

As described above, in a full monitor device for epilepsy, EEG, respiratory and cardiac (ECG) physiologic signals are simultaneously monitored and processed by different algorithms. A seizure-detection algorithm detects seizure activity in the EEG signals. A second algorithm detects heart-rate changes, ECG abnormalities, or unique waveform patterns in the ECG signals, which may or may not be coincident with seizures. Additionally, a third algorithm detects minute ventilation, respiration rate and apnea, which also may or may not be coincident with seizures.

By default, the EEG is considered a ‘primary signal’—detections from this signal are used to represent seizure. The ECG and respiratory signals are ‘secondary signals’—it is not initially known whether events detected in these two signals are useful for seizure detection. In a treatment setting, the patient's clinician considers the stored signals and data to determine if processing the ECG and respiratory signals provides added benefit in improving detection performance.

To make this determination, the patient is monitored until a sufficient number of detections in one or both of the data streams are observed (number of required events is programmable). Events detected in the EEG data stream may be classified by the user, via the programmer interface, to indicate whether they are clinical seizures (TP-C), sub-clinical seizures (TP-N), or false positive detections (FP). Likewise, events detected in the ECG and respiratory signals may be classified to indicate type of abnormality detected.

The concordance between the EEG seizure detections and ECG and respiratory signals is then evaluated. This is accomplished in one of two ways:

The relation between the EEG and ECG detections is initially unknown. Determination of the relationship between EEG and ECG may be performed with post processing or in real time.

In the post processing embodiment, automated matching tests are performed to identify the temporal relationship of detections in the different data streams. The matching tests identify the number of EEG detections that are within a specified time period with ECG or respiratory abnormalities (EEG-ECG Match or EEG-Respiratory Match, see 864 and 868 FIG. 38), and those that are not (EEG detect-ECG Normal or EEG detect-Respiratory Normal). For matched detections, the time difference between EEG detection onset and ECG or respiratory detection onset is computed (detection latency). The number of detected events in the ECG or respiratory signals, independent of EEG triggered events, are also computed (ECG Un-matched or Respiratory Un-Matched, see 870 FIG. 38).

With the real time implementation, the device controls a flag set by the seizure-detection algorithm operating on EEG signals. The flag is a real-time indicator of the subject's seizure state (1=in EEG detection state; 0=out of EEG detection state). In real-time, the device monitors the co-occurrence of the EEG and ECG/respiratory detection states.

The following conditions are assessed:

Brain-Cardiac Match—The EEG event (e.g., seizure) is classified as matched with ECG event if the ECG detection state occurs during an EEG detection state or within a specified time period of an EEG detection state.

Brain-Respiratory Match—The EEG event (e.g., seizure) is classified as matched with respiratory event if the respiratory detection state occurs during an EEG detection state or within a specified time period of an EEG detection state.

Brain Detect-Cardiac Normal—The EEG event (e.g., seizure) is classified as matched with normal ECG if no ECG detection state occurs during an EEG detection state or within a specified time period of an EEG detection state.

Brain Detect-Respiratory Normal—The EEG event (e.g., seizure) is classified as matched with normal respiration if no respiratory detection state occurs during an EEG detection state or within a specified time period of the EEG detection state.

Cardiac Un-Matched—An ECG event is classified as un-matched to EEG event (e.g., seizure) if no EEG detection state occurs during the ECG detection state or within a specified time period of an ECG detection state.

Respiratory Un-Matched—A respiratory event is classified as un-matched to EEG event (e.g., seizure) if no EEG detection state occurs during the respiratory detection state or within a specified time period of the respiratory detection state.

After EEG-ECG or EEG-respiratory matching has been performed, the physician programmer indicates whether the following conditions are true: (1) a high rate of concordance between detections in the EEG and ECG data streams (or between the EEG and respiratory data streams); (2) earlier detection in the ECG signal (or respiratory signal) relative to neurological event onset as indicated in the EEG signal; and (3) a low rate of FP's in the ECG signal (or in the respiratory signal). If these conditions are all true, this may indicate that the ECG signal (or respiratory signal) provides value in neurological event detection (e.g., seizure detection).

Using this information, the physician may choose to activate the ECG algorithm or activate the respiration algorithm—that is, enable it as a primary signal for use in neurological event detection. Determination of whether to “add in” the ECG or respiratory signals (activate it in combination with the EEG signal) for seizure monitoring or treatment is based on satisfying one or more of the above stated conditions. This process can be automated by defining programmable threshold values for each of the stated conditions.

Note that ECG detection and respiratory detection may both be enabled or activated for neurological event detection if they both meet the conditions above.

The physician may decide not to enable the ECG/respiratory algorithms if the matching tests show no additional improvements in detection performance using the ECG or respiratory signals, or if specificity in the ECG/respiratory signals is low. In such cases, the physician may enable a mode of passive ECG recording, with the intended use of documenting cardiovascular changes during stimulation periods in the EEG.

FIG. 40A shows a process 971 for determining whether to enable the cardiac or respiratory detection algorithms for neurological event detection. At block 974 the medical device system monitors a brain signal and, cardiac or respiratory signals. At block 975 detections in any of the 3 signals (brain, cardiac, respiratory) triggers loop recording. Determination of the bounds of the neurological, cardiac and respiratory events may be performed in various ways. In one embodiment this determination of the bounds of events may be performed by a physician. In another embodiment, such determination of the bounds of the events may be performed by detection algorithms executed by a processor. Block 991 represents this choice between physician marked events and algorithm marked events. In the physician marking embodiment, the loop recording stored data must be uplinked to an external device such as a programmer or other computer. Upon uplinking the loop recording stored data, the physician may score the onset, offset or other reference points in the brain signal at block 976. The physician may also classify the events as related or not to the particular neurological event being targeted. A matching test (brain detections versus cardiac or respiratory detections) is executed at block 977. The brain inputs to the matching test may be either physician markings (e.g., onset, offset of neurological event) or the automated scores from the neurological event detection algorithm. The matching test results from block 977 result in a summary of comparisons made between the brain and cardiac detections (or between the brain and respiratory detections). At block 978 the matching test results are evaluated. The evaluation at block 978 includes blocks 979, 980 and 981 (i.e., blocks 979, 980 and 981 are components of block 978. At block 979 concordance between brain and cardiac/respiratory detections is determined. At block 980 a cardiac or respiratory false positive rate (relative to the neurological signal) is evaluated using the cardiac un-matched events or the respiratory un-matched events in the cardiac or respiratory signals. At block 981 cardiac/respiratory latency is evaluated for the matched detections. At block 982, neurological event detection improvement using cardiac or respiration signals is considered based upon the above determinations. If use of cardiac signals or respiratory signals does not improve neurological event detection (“NO” condition), then the physician or other user may maintain or disable the cardiac event detection algorithm monitoring at block 983. If at block 982 the result is YES, the cardiac or respiratory signal is activated for neurological event monitoring or treatment.

Process 871 in FIG. 40B is one specific embodiment of process 971 in FIG. 40A. Process 871 is a process for determining whether to enable the ECG or respiratory detection algorithms for seizure detection. At block 874 the full monitor monitors EEG and ECG or respiratory signals. At block 875 detections in any of the 3 signals (EEG, ECG or respiratory) triggers loop recording. Determination of the bounds of the seizure, ECG and respiratory events may be performed in various ways. In one embodiment this determination of the bounds of a seizure may be performed by a physician. In another embodiment, such determination of the bounds of the events may be performed by detection algorithms executed by a processor. Block 891 represents this choice between physician marked events and algorithm marked events. In the physician marking embodiment, the loop recording stored data must be uplinked to an external device such as a programmer or other computer. Upon uplinking the loop recording stored data, the physician may score the onset, offset or other reference points in the EEG signal at block 876. The physician may also classify the events as seizure related or not. A matching test (EEG detections versus ECG or respiratory detections) is executed at block 877. The EEG inputs to the matching test may be either physician scores (e.g., onset, offset of seizure) or the automated scores from the neurological event detection algorithm. The matching test results from block 877 result in a summary of comparisons made between the EEG and ECG detections (or between the EEG and respiratory detections). At block 878 the matching test results are evaluated. The evaluation at block 878 includes blocks 879, 880 and 881 (i.e., blocks 879, 880 and 881 are components of block 878. At block 879 concordance between EEG and ECG/respiratory detections is determined. At block 880 an ECG false positive rate (relative to the neurological signal) is evaluated using the unmatched events in the ECG or respiratory signals. At block 881 ECG/respiratory latency is evaluated for the matched detections. At block 882, seizure detection improvement using ECG or respiration signals is considered based upon the above determinations. If use of ECG signals or respiratory signals does not improve seizure detection (“NO” condition), then the physician or other user may maintain or disable the ECG algorithm monitoring at block 883. The monitor begins monitoring or treatment at block 885. If at block 882 the result is YES, the ECG or respiratory signal is activated for seizure monitoring.

Monitor+Treatment (Brain)

FIG. 41 is a block diagram of the electronic circuitry that makes up full Monitor/Brain Therapy device 300 (FIG. 11) in accordance with the presently disclosed alternative embodiment of the invention. As can be seen from FIG. 41, Monitor/Brian Therapy device 300 comprises a primary control circuit 720 that is described herein above in conjunction with FIG. 26. In addition the Monitor/Brain Therapy device 300 of FIG. 41 also includes an amplifier 725 to amplify and sense EEG signals from a cranially implanted lead (one embodiment of a brain monitoring element 18) and a therapy module for providing therapy to the brain. The therapy module may be a drug delivery pump or an electrical stimulator or a brain cooling mechanism or other components depending on the treatment modality. In the embodiment of FIG. 41, the therapy module is an output stimulator 729 for stimulation of the brain. The CPU 732, in conjunction with software program in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, provides preprogrammed stimulation therapy to the patient's brain via a brain lead that may be the same as monitoring element 18, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description as described below in association with FIG. 56.

FIG. 42 is a block diagram of the electronic circuitry that makes up full Monitor/Brain Therapy device 320 (FIG. 12A) in accordance with the presently disclosed alternative embodiment of the invention. As can be seen from FIG. 42, Monitor/Brain Therapy device 320 comprises a primary control circuit 720 and MV circuit 722 that are described herein above in conjunction with FIG. 28. In addition the Monitor/Brain Therapy device of FIG. 42 also includes an amplifier 725 to amplify and sense EEG signals from a cranially implanted monitoring element 18 and an output stimulator 729 to provide brain stimulation. The CPU 732, in conjunction with software program in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, provides preprogrammed stimulation therapy to the patient's brain via a lead that may be the same as brain monitoring element 18, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description as described below in association with FIG. 56.

FIG. 43 is a block diagram of the electronic circuitry that makes up full Monitor/Brain Therapy device 321 (FIG. 12B) in accordance with the presently disclosed alternative embodiment of the invention. As can be seen from FIG. 43, Monitor/Brain Therapy device 321 in combination with a cranially implanted Monitor/Brain Therapy unit 26 in a patient 10 includes a primary control circuit 720 and MV circuit 722 that are described herein above in conjunction with FIG. 28. A 2-way wireless telemetry communication link 30 connects the Monitor/Therapy unit 26 and Monitor/Brain Therapy unit 321 via antennas 736. The wireless communication link 30 may consist of an RF link (such as described in U.S. Pat. No. 5,683,432 “Adaptive Performance-Optimizing Communication System for Communicating with an Implantable Medical Device” to Goedeke, et al, an electromagnetic/ionic transmission (such as described in U.S. Pat. No. 4,987,897 “Body Bus Medical Device Communication System” to Funke) or acoustic transmission (such as described in U.S. Pat. No. 5,113,859 “Acoustic Body Bus Medical Device Communication System” to Funke). Monitor/Brain Therapy unit 26 contains an amplifier 725 to amplify and sense EEG signals from a cranially implanted brain monitoring element 18 such as a lead and an output stimulator 729 for stimulation of the brain. Monitor 26 may be constructed as substantially described in US Publication No. 20040176817 “Modular implantable medical device” to Wahlstrand et al. or U.S. Pat. No. 5,782,891 “Implantable Ceramic Enclosure for Pacing, Neurological and Other Medical Applications in the Human Body” to Hassler, et al or U.S. Pat. No. 6,427,086 “Means and Method for the Intracranial Placement of a Neurostimulator” to Fischell. et al. EEG sensing is accomplished by the use of integrated electrodes in the housing of monitor 26 or, alternatively, by a brain monitoring element 18 such as a cranially implanted leads.

Specifically, CPU 732, in conjunction with software program in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, provides preprogrammed stimulation therapy to the patient's brain via a lead or other therapy delivery device (that could be the same as brain monitoring element 18), formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description as described below in association with FIG. 56.

FIG. 44 is a block diagram of one embodiment of the electronic circuitry that makes up full Monitor/Brain Therapy device 340 with a brain monitoring element 18 (e.g., lead) and cardiac or respiratory monitoring element 14 such as sensor stub 20 (FIG. 13) in accordance with the presently disclosed alternative embodiment of the invention. As can be seen from FIG. 44, Monitor/Brain Therapy device 340 comprises a primary control circuit 720 and MV circuit 722 that were described herein above in conjunction with FIG. 28. In addition, the full Monitor/Brain Therapy device 340 of FIG. 44 also includes an amplifier 725 to amplify and sense EEG signals from a brain monitoring element 18 such as a cranially implanted lead. Additionally, the full Monitor/Brain Therapy device 340 of FIG. 44 also includes a stimulator 729 for providing stimulation to the brain through brain monitoring element 18 such as a cranially implanted lead. The CPU 732, in conjunction with a software program resident in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, provides preprogrammed stimulation therapy to the patient's brain via a therapeutic element such as brain monitoring element 18 which may be a lead, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description as described below in association with FIG. 56.

FIG. 45 is a block diagram of one embodiment of the electronic circuitry that makes up external patch 160/full Monitor/Brain Therapy device 360 with a brain monitoring element 18 that may be used for sensing and application of therapy (in the case of therapy being electrical stimulation) (FIG. 8) in accordance with the presently disclosed alternative embodiment of the invention. As can be seen from FIG. 45, Monitor/Brain Therapy device 360 comprises a primary control circuit 720 and external patch comprises a cardiac/MV (minute ventilation) circuit 160, the functions of which have been described in detail above in conjunction with the system of FIG. 28. Intrinsic cardiac signals are sensed by electrodes affixed to the patient's skin, amplified by amplifier 724, sent to primary control circuit 720 and processed by CPU 732 and software program resident in RAM/ROM 730. Cardiac anomalies are detected such as heart rate variability, QT variability, QT_(C), sinus arrest, and various arrhythmias such as sinus, atrial and ventricular tachycardias. Respiration sensing is accomplished by low pass filtering the sensed and amplified intrinsic cardiac signals as shown in FIG. 27 or, alternatively, by using the MV/Z measurement circuitry of external patch 160 as described above in connection with FIG. 28. Respiration anomalies (such as reduced or cessation of tidal volume and apnea) are evaluated and detected by CPU 732 and software resident in RAM/ROM 730.

The CPU 732, in conjunction with a software program resident in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, provides preprogrammed stimulation therapy to the patient's brain via lead 18, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description as described below in association with FIG. 56.

The circuitry and function of the device 340 shown in FIG. 44 and described herein above may also be used for the full Monitor/Brain Therapy device 380 with integrated electrode 24 brain lead 18 (FIG. 15). As described above in association with core Monitor 340, thoracic impedance via impedance/voltage converter as measured from the case of monitor 340 to the integrated electrode 24 using a sampling frequency of approximately 16 Hz as substantially described in U.S. Pat. No. 4,596,251 “Minute Ventilation Dependant Rate Responsive Pacer” to Plicchi, et al. The Monitor 380 of this alternative embodiment utilizes the same circuitry of Monitor 340 but connected to the integrated electrode 24 on brain lead 18 instead of the sensor stub of Monitor 340.

Upon detection of either/or a cardiac or respiration anomaly, CPU 732, under control of firmware resident in RAM/ROM 730, will initiate recording of the appropriate diagnostic information into RAM of RAM/ROM 730, provides preprogrammed stimulation therapy to the patient's brain via lead 18, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description as described below in association with FIG. 56.

FIG. 46 is a block diagram of the electronic circuitry that makes up full Monitor/Brain Therapy device 400 (FIG. 20) in accordance with the presently disclosed alternative embodiment of the invention. As can be seen from FIG. 46, Monitor/Brian Therapy device 400 comprises a primary control circuit 720 (sensing cardiac and respiration parameters) that is described herein above in conjunction with FIG. 26. In addition the Monitor/Brain Therapy device 400 connects via a 2-way wireless communication link 30 to a cranially implanted EEG sensor and brain stimulator 26. EEG senor and brain stimulator 26 contains an amplifier 725 to amplify and sense EEG signals from a cranially implanted lead 18 and an output stimulator 729 for stimulation of the brain. The CPU 732, in conjunction with software program in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, provides preprogrammed stimulation therapy to the patient's brain via lead 18, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description as described below in association with FIG. 56.

FIG. 47 is a block diagram of the electronic circuitry that makes up full Monitor/Brain Therapy device 420 (FIG. 21) in accordance with the presently disclosed alternative embodiment of the invention. As can be seen from FIG. 47, Monitor/Brian Therapy device 420 comprises a primary control circuit 720 (sensing cardiac and respiration parameters) that is configured as an external patch affixed to a patient and whose function is described herein above in conjunction with FIG. 26. In addition, the Monitor/Brain Therapy device 420 comprises to a cranially implanted EEG sensor and brain stimulator 26 connected to the primary control circuit 720 via a 2-way wireless communication link 30. The wireless communication link 30 may consist of an RF link (such as described in U.S. Pat. No. 5,683,432 “Adaptive Performance-Optimizing Communication System for Communicating with an Implantable Medical Device” to Goedeke, et al.), an electromagnetic/ionic transmission (such as described in U.S. Pat. No. 4,987,897 “Body Bus Medical Device Communication System” to Funke) or acoustic transmission (such as described in U.S. Pat. No. 5,113,859 “Acoustic Body Bus Medical Device Communication System” to Funke). EEG sensor and brain stimulator 26 contains an amplifier 725 to amplify and sense EEG signals from a cranially implanted lead 18 and an output stimulator 729 for stimulation of the brain. The CPU 732, in conjunction with software program in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, provides preprogrammed stimulation therapy to the patient's brain via lead 18, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description as described below in association with FIG. 56.

Monitor+Treatment (Brain+Respiration)

FIG. 48 is a block diagram of the electronic circuitry that makes up full Monitor/Brain and Respiration Therapy device 440 (FIG. 16A) in accordance with the presently disclosed alternative embodiment of the invention. As can be seen from FIG. 48, Monitor/Brain and Respiration Therapy device 440 comprises a primary control circuit 720 and MV circuit 722 whose function was described herein above in conjunction with FIG. 28. In addition the Monitor/Brain and Respiration Therapy device of FIG. 48 also includes an amplifier 725 to amplify and sense EEG signals from a cranially implanted lead 18 and an output stimulator 729 to provide brain stimulation via cranially implanted lead 18 and phrenic nerve stimulation via respiration lead 28. The CPU 732, in conjunction with software program in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, provides preprogrammed stimulation therapy to the patient's brain via lead 18 and stimulation of the patient's phrenic nerve via respiration lead 28, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. Optionally, lead 28 may connect to the diaphragm to provide direct diaphragmatic stimulation. See flow diagram and description as described below in association with FIG. 56.

FIG. 49 is a block diagram of the electronic circuitry that makes up full Monitor/Brain and Respiration Therapy device 441 (FIG. 16B) in accordance with the presently disclosed alternative embodiment of the invention. As can be seen from FIG. 49, Monitor/Brain and Respiration Therapy device 441 in combination with a cranially implanted Monitor/Brain Therapy unit 26 in a patient 10 includes a primary control circuit 720 and MV circuit 722 that are described herein above in conjunction with FIG. 28. A 2-way wireless telemetry communication link 30 connects the Monitor/Therapy unit 26 and Monitor/Brain and Respiration Therapy unit 441 via antennas 736. The wireless communication link 30 may consist of an RF link (such as described in U.S. Pat. No. 5,683,432 “Adaptive Performance-Optimizing Communication System for Communicating with an Implantable Medical Device” to Goedeke, et al), an electromagnetic/ionic transmission (such as described in U.S. Pat. No. 4,987,897 “Body Bus Medical Device Communication System” to Funke) or acoustic transmission (such as described in U.S. Pat. No. 5,113,859 “Acoustic Body Bus Medical Device Communication System” to Funke). Monitor/Brain Therapy unit 26 contains an amplifier 725 to amplify and sense EEG signals from a cranially implanted lead 18 and an output stimulator 729 for stimulation of the brain. Monitor 26 may be constructed as substantially described in US Publication No. 20040176817 “Modular implantable medical device” to Wahlstrand et al. or U.S. Pat. No. 5,782,891 “Implantable Ceramic Enclosure for Pacing, Neurological and Other Medical Applications in the Human Body” to Hassler, et al or U.S. Pat. No. 6,427,086 “Means and Method for the Intracranial Placement of a Neurostimulator” to Fischell. et al. EEG sensing is accomplished by the use of integrated electrodes in the housing of monitor 26 or, alternatively, by cranially implanted leads 18.

Specifically, CPU 732, in conjunction with software program in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, provides preprogrammed stimulation therapy to the patient's brain via lead 18 and to the phrenic nerve via respiration lead 28, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. Optionally, lead 28 may connect to the diaphragm to provide direct diaphragmatic stimulation. See flow diagram and description as described below in association with FIG. 56.

FIG. 50 is a block diagram of the electronic circuitry that makes up full Monitor/Brain and Respiration Therapy device 460 with a brain lead 18, phrenic nerve lead 28 and sensor stub 20 (FIG. 17) in accordance with the presently disclosed alternative embodiment of the invention. As can be seen from FIG. 50, Monitor/Brain and Respiration Therapy device 460 comprises a primary control circuit 720 and MV circuit 722 whose function was described herein above in conjunction with FIG. 28. In addition, the full Monitor/Brain and Respiration Therapy device 460 of FIG. 50 also includes an amplifier 725 to amplify and sense EEG signals from a cranially implanted lead 18. Additionally, the full Monitor/Brain Therapy device 340 of FIG. 44 also includes a stimulator 729 for providing stimulation to the brain through cranially implanted lead 18 and phrenic nerve stimulation via respiration lead 28. The CPU 732, in conjunction with a software program resident in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, provides preprogrammed stimulation therapy to the patient's brain via lead 18 and stimulation of the patient's phrenic nerve via respiration lead 28, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description as described below in association with FIG. 56.

The circuitry and function of the device 460 shown in FIG. 50 and described herein above may also be used for the full Monitor/Brain and Respiration Therapy device 480 with integrated electrode 24 brain lead 18 and phrenic nerve lead 28 (FIG. 18). As described above in association with Monitor/Brain and Respiration Therapy device 460, thoracic impedance via impedance/voltage converter as measured from the case of monitor 480 to the integrated electrode 24 using a sampling frequency of approximately 16 Hz as substantially described in U.S. Pat. No. 4,596,251 “Minute Ventilation Dependant Rate Responsive Pacer” to Plicchi, et al. The Monitor/Brain and Respiration Therapy device 480 of this alternative embodiment utilizes the same circuitry of Monitor/Brain and Respiration Therapy device 460 but connected to the integrated electrode 24 on brain lead 18 instead of the sensor stub 20 of Monitor/Brain and Respiration Therapy device 340.

Upon detection of either/or a cardiac or respiration anomaly, CPU 732, under control of firmware resident in RAM/ROM 730, will initiate recording of the appropriate diagnostic information into RAM of RAM/ROM 730, provides preprogrammed stimulation therapy to the patient's brain via lead 18 and stimulation of the patient's phrenic nerve via respiration lead 28, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description as described below in association with FIG. 56.

The circuitry and function of the device 460 shown in FIG. 50 and described herein above may also be used for the full Monitor/Brain and Respiration Therapy device 500 with brain lead 18 and integrated electrode 24 phrenic nerve lead 28 (FIG. 19). As described above in association with Monitor/Brain and Respiration Therapy device 460, thoracic impedance via impedance/voltage converter as measured from the case of monitor 500 to the integrated electrode 24 using a sampling frequency of approximately 16 Hz as substantially described in U.S. Pat. No. 4,596,251 “Minute Ventilation Dependant Rate Responsive Pacer” to Plicchi, et al. The Monitor/Brain and Respiration Therapy device 500 of this alternative embodiment utilizes the same circuitry of Monitor/Brain and Respiration Therapy device 460 but connected to the integrated electrode 24 on phrenic nerve lead 28 instead of the sensor stub 20 of Monitor/Brain and Respiration Therapy device 340.

Upon detection of either/or a cardiac or respiration anomaly, CPU 732, under control of firmware resident in RAM/ROM 730, will initiate recording of the appropriate diagnostic information into RAM of RAM/ROM 730, provides preprogrammed stimulation therapy to the patient's brain via lead 18 and stimulation of the patient's phrenic nerve via respiration lead 28, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description as described below in association with FIG. 56.

Monitor+Treatment (Brain+Cardiac)

FIG. 51 is a block diagram of the electronic circuitry that makes up full Monitor/Brain and Cardiac Therapy device 520 (FIG. 24A) in accordance with the presently disclosed alternative embodiment of the invention. As can be seen from FIG. 51, Monitor/Brain and Cardiac Therapy device 520 comprises a primary control circuit 720 and MV circuit 722 whose function is described herein above in conjunction with FIG. 28 and U.S. Pat. No. 5,271,395 “Method and Apparatus for Rate Responsive Cardiac Pacing” to Wahlstrand et al. In addition, the Monitor/Brain and Cardiac Therapy device of FIG. 51 also includes an amplifier 725 to amplify and sense EEG signals from a cranially implanted lead 18 and an output stimulator 729 to provide brain stimulation. The CPU 732, in conjunction with software program in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, provides preprogrammed stimulation therapy to the patient's brain via lead 18 and stimulation to the patient's heart via cardiac lead(s) 16, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description as described below in association with FIG. 54.

FIG. 52 is a block diagram of the electronic circuitry that makes up full Monitor/Brain and Cardiac Therapy device 521 (FIG. 24B) in accordance with the presently disclosed alternative embodiment of the invention. As can be seen from FIG. 52, Monitor/Brain and Cardiac Therapy device 521 in combination with a cranially implanted Monitor/Brain Therapy unit 26 in a patient 10 includes a primary control circuit 720 and MV circuit 722 that are described herein above in conjunction with FIG. 28. A 2-way wireless telemetry communication link 30 connects the Monitor/Therapy unit 26 and Monitor/Brain and Cardiac Therapy unit 521 via antennas 736. The wireless communication link 30 may consist of an RF link (such as described in U.S. Pat. No. 5,683,432 “Adaptive Performance-Optimizing Communication System for Communicating with an Implantable Medical Device” to Goedeke, et al ), an electromagnetic/ionic transmission (such as described in U.S. Pat. No. 4,987,897 “Body Bus Medical Device Communication System” to Funke) or acoustic transmission (such as described in U.S. Pat. No. 5,113,859 “Acoustic Body Bus Medical Device Communication System” to Funke). Monitor/Brain Therapy unit 26 contains an amplifier 725 to amplify and sense EEG signals from a cranially implanted lead 18 and an output stimulator 729 for stimulation of the brain. Monitor 26 may be constructed as substantially described in US Publication No. 20040176817 “Modular implantable medical device” to Wahlstrand et al. or U.S. Pat. No. 5,782,891 “Implantable Ceramic Enclosure for Pacing, Neurological and Other Medical Applications in the Human Body” to Hassler, et al or U.S. Pat. No. 6,427,086 “Means and Method for the Intracranial Placement of a Neurostimulator” to Fischell. et al. EEG sensing is accomplished by the use of integrated electrodes in the housing of monitor 26 or, alternatively, by cranially implanted leads 18.

Specifically, CPU 732, in conjunction with software program in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, provides preprogrammed stimulation therapy to the patient's brain via lead 18 and cardiac stimulation via cardiac leads 16, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description as described below in association with FIG. 56.

Alternatively, the device as described above in connection to the Monitor and Treatment (Brain and Cardiac) system of FIG. 52 may include a pacemaker/cardioverter/defibrillator (PCD) to enable the termination of cardiac arrhythmias during, or prior to, neurological events. The PCD may be of the type as substantially described in U.S. Pat. No. 5,545,186 “Prioritized Rule Based Method and Apparatus for Diagnosis and Treatment of Arrhythmias” to Olson; U.S. Pat. No. 5,354,316 “Method and Apparatus for Detection and Treatment of Tachycardia and fibrillation” to Kiemel or U.S. Pat. No. 5,314,430 “Atrial Defibrillator Employing Transvenous and Subcutaneous Electrodes and Method of Use” to Bardy. In one embodiment of the present invention, the PCD arrhythmia detection circuitry/algorithms are enabled upon the sensing of the onset or impending onset of a seizure. Upon seizure termination, the arrhythmia detection circuitry/algorithms are turned off.

FIG. 53 is a block diagram of the electronic circuitry that makes up full Monitor/Brain and Cardiac Therapy device 540 (FIG. 22) in accordance with the presently disclosed alternative embodiment of the invention. The system as shown in FIG. 53 is used for patients temporarily at risk of sudden death, for example, while the patient's physician is trying different epileptic drugs and titrating dosages to eliminate/minimize seizures or their severity. As can be seen from FIG. 53, Monitor/Brain and Cardiac Therapy device 540 comprises patient worn vest defibrillator 34 containing primary control circuit 720 whose function is described herein above in conjunction with FIG. 26 and in more detail in U.S. Pat. No. 6,280,461 “Patient-Worn Energy Delivery Apparatus” to Glegyak, et. In addition the Monitor/Brain and Cardiac Therapy device connects via a 2-way wireless communication link 30 to a cranially implanted brain stimulator 540. The wireless communication link 30 may consist of an RF link (such as described in U.S. Pat. No. 5,683,432 “Adaptive Performance-Optimizing Communication System for Communicating with an Implantable Medical Device” to Goedeke, et al ), an electromagnetic/ionic transmission (such as described in U.S. Pat. No. 4,987,897 “Body Bus Medical Device Communication System” to Funke) or acoustic transmission (such as described in U.S. Pat. No. 5,113,859 “Acoustic Body Bus Medical Device Communication System” to Funke). EEG senor and brain stimulator 540 contains an amplifier 725 to amplify and sense EEG signals from a cranially implanted lead 18 and an output stimulator 729. The CPU 732, in conjunction with software program in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, provides preprogrammed stimulation therapy to the patient's brain via lead 18 and defibrillation therapy via patient worn vest 34, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description as described below in association with FIG. 56.

The circuitry and function of the device 540 shown in FIG. 53 and described herein above may also be used for the full Monitor/Brain and Cardiac Therapy device 560 with a cranially implanted stimulator in 2-way communication with an leadless subcutaneous implantable defibrillator 36 (ie, “lifeboat”, FIG. 23). The system described in connection with this embodiment is used for patients temporarily at risk of sudden death, for example, while the patient's physician is trying different epileptic drugs and titrating dosages to eliminate/minimize seizures or their severity. As described above in conjunction with FIG. 53, Monitor/Brian and Cardiac Therapy device 560 comprises a leadless defibrillator 36 containing primary control circuit 720 whose function is described herein above in conjunction with FIG. 26 and in more detail in U.S. Pat. No. 6,647,292 “Unitary Subcutaneous only Implantable Cardioverter-Defibrillator and Optional Pacer” to Bardy.

The Monitor/Brain and Cardiac Therapy device connects via a 2-way wireless communication link 30 to a cranially implanted brain stimulator 560. The wireless communication link 30 may consist of an RF link (such as described in U.S. Pat. No. 5,683,432 “Adaptive Performance-Optimizing Communication System for Communicating with an Implantable Medical Device” to Goedeke, et al ), an electromagnetic/ionic transmission (such as described in U.S. Pat. No. 4,987,897 “Body Bus Medical Device Communication System” to Funke) or acoustic transmission (such as described in U.S. Pat. No. 5,113,859 “Acoustic Body Bus Medical Device Communication System” to Funke). EEG senor and brain stimulator 560 contains an amplifier 725 to amplify and sense EEG signals from a cranially implanted lead 18 and an output stimulator 729. The CPU 732, in conjunction with software program in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, provides preprogrammed stimulation therapy to the patient's brain via lead 18 and defibrillation therapy via implanted defibrillator 36, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. See flow diagram and description as described below in association with FIG. 56.

Monitor+Treatment (Brain+Respiration+Cardiac)

FIG. 54 is a block diagram of the electronic circuitry that makes up full Monitor/Brain, Respiration and Cardiac Therapy device 580 (FIG. 25A) in accordance with the presently disclosed alternative embodiment of the invention. As can be seen from FIG. 54, Monitor/Brain, Respiration and Cardiac Therapy device 580 comprises a primary control circuit 720 and MV circuit 722 whose function was described herein above in conjunction with FIG. 28. In addition the Monitor/Brain, Respiration and Cardiac Therapy device of FIG. 54 also includes an amplifier 725 to amplify and sense EEG signals from a cranially implanted lead 18 and an output stimulator 729 to provide brain stimulation via cranially implanted lead 18 and phrenic nerve stimulation via respiration lead 28. The CPU 732, in conjunction with software program in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, provides preprogrammed stimulation therapy to the patient's brain via lead 18, stimulation of the patient's phrenic nerve via respiration lead 28 and stimulation of the patient's heart via cardiac leads 16, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. Optionally, lead 28 may connect to the diaphragm to provide direct diaphragmatic stimulation. See flow diagram and description as described below in association with FIG. 56.

FIG. 55 is a block diagram of the electronic circuitry that makes up full Monitor/Brain, Respiration and Cardiac Therapy device 581 (FIG. 25B) in accordance with the presently disclosed alternative embodiment of the invention. As can be seen from FIG. 55, Monitor/Brain, Respiration and Cardiac Therapy device 581 in combination with a cranially implanted Monitor/Brain Therapy unit 26 in a patient 10 includes a primary control circuit 720 and MV circuit 722 that are described herein above in conjunction with FIG. 28. A 2-way wireless telemetry communication link 30 connects the Monitor/Therapy unit 26 and Monitor/Brain, Respiration and Cardiac Therapy unit 581 via antennas 736. The wireless communication link 30 may consist of an RF link (such as described in U.S. Pat. No. 5,683,432 “Adaptive Performance-Optimizing Communication System for Communicating with an Implantable Medical Device” to Goedeke, et al ), an electromagnetic/ionic transmission (such as described in U.S. Pat. No. 4,987,897 “Body Bus Medical Device Communication System” to Funke) or acoustic transmission (such as described in U.S. Pat. No. 5,113,859 “Acoustic Body Bus Medical Device Communication System” to Funke). Monitor/Brain Therapy unit 26 contains an amplifier 725 to amplify and sense EEG signals from a cranially implanted lead 18 and an output stimulator 729 for stimulation of the brain. Monitor 26 may be constructed as substantially described in US Publication No. 20040176817 “Modular implantable medical device” to Wahlstrand et al. or U.S. Pat. No. 5,782,891 “Implantable Ceramic Enclosure for Pacing, Neurological and Other Medical Applications in the Human Body” to Hassler, et al or U.S. Pat. No. 6,427,086 “Means and Method for the Intracranial Placement of a Neurostimulator” to Fischell. et al. EEG sensing is accomplished by the use of integrated electrodes in the housing of monitor 26 or, alternatively, by cranially implanted leads 18.

Specifically, CPU 732, in conjunction with software program in RAM/ROM 730, integrates the information from the sensed cardiac, respiration and EEG signals, detects the onset of cerebral, cardiac or respiratory anomalies, provides preprogrammed stimulation therapy to the patient's brain via lead 18, to the phrenic nerve via respiration lead 28 and to the heart via cardiac leads 16, formats and stores diagnostic data for later retrieval by the patient's clinician and, optionally, may warn or alert the patient, patient caregiver or remote monitoring location. Optionally, lead 28 may connect to the diaphragm to provide direct diaphragmatic stimulation. See flow diagram and description as described below in association with FIG. 56.

FIG. 56 is a flow diagram 850 showing operation of a full monitor/therapy sensing and monitoring cardiac, respiration and electroencephalogram parameters for the detection of neurological events as shown and described in embodiments in FIGS. 11-25 above. The blocks 802-808 relating to the identification of cardiac activity, and blocks 816-822 relating to identification of respiratory activity, may be activated or deactivated according to the determination of whether they improve the detection of the neurological disorder (see for example the discussion regarding determining concordance). It is noted that the particular detection scheme used for each of the physiologic signals (brain, heart, respiratory) is not restricted to the examples provided here.

In one embodiment, beginning at block 802, the interval between sensed cardiac signals are measured. At block 804, a rate stability measurement is made on each cardiac interval utilizing a heart rate average from block 806. At block 808, a rate stable decision is made based upon preprogrammed parameters. If YES (heart rate is determined to be stable), the flow diagram returns to the HR Measurement block 802. If NO, the rate stability information is provided to Determine Therapy and Duration block 830.

At block 816, thoracic impedance is continuously measured in a sampling operation. At block 818, a MV and respiration rate calculation is made. At block 822, a pulmonary apnea decision is made based upon preprogrammed criteria. If NO (no apnea detected), the flow diagram returns to MV Measurement block 816. If YES, the occurrence of apnea and MV information is provided to Determine Therapy and Duration block 830.

At block 824, the electroencephalogram is sensed and measured. An EEG calculation is performed at block 826. The seizure detection algorithm is executed at block 826. At block 828, a seizure episode is determined. If NO (no seizure detected), the flow diagram returns to EEG Measurement block 824. If YES, the occurrence of a seizure is provided to Determine Therapy and Duration block 830.

Based upon the data presented to it, Determine Therapy and Duration block 830 determines the type of therapy and the duration to block 832, which controls the start of the therapy by evaluating the severity and ranking of each event (i.e., maximum ratio, duration of seizure detection, spread, number of clusters per unit time, number of detections per cluster, duration of an event cluster, duration of a detection, and inter-seizure interval) per co-pending U.S. patent application Publication No. 20040133119 “Scoring of sensed neurological signals for use with a medical device system”

to Osorio, et al incorporated herein by reference in its entirety. Block 834 monitors the completion of the determined therapy. If the therapy is not complete, control returns to block 834. If the therapy is determined to be complete, block 834 returns the flow diagram to blocks 802 (Measure HR), 816 (Measure Impedance) and 824 (Measure EEG) to continue the monitoring of cardiac, respiratory and brain signal parameters.

Therapy may consist of neural stimulation, cardiac pacing, cardioversion/defibrillation, and drug delivery via a pump, brain cooling, or any combination of therapies.

When block 830 determines that a therapy is to be initiated Format Diagnostic Data block 812 formats the data from the cardiac, respiration and EEG monitoring channels, adds a time stamp (ie, date and time), type and duration of therapy and provides the data to block 814 where the data is stored in RAM memory for later retrieval by a clinician via telemetry. Optionally, block 812 may add examples of intrinsic ECG, respiration or EEG signals recorded during a sensed episode/seizure.

The physician may program the devices shown above in relation to FIGS. 11-25 and 41-55 to allow the ECG/respiratory detectors be enabled to trigger the delivery of therapy (i.e., stimulation or drug delivery) to the patient's brain, with goal of aborting seizures earlier or limiting their severity than if using EEG signal detection alone. Either EEG, respiratory or ECG detections may trigger therapy to the brain, depending on which occurs first. The physician may choose the type of ECG or respiratory event to use for triggering therapy to the brain.

Application of Therapy to the Brain Based on Cardiac or Respiratory Signals and Termination of such Therapy

In the present invention of the devices shown above in relation to FIGS. 11-25 and 41-55, the device is able to terminate or change the cardiac/respiratory initiated treatment, directed at the brain, if a neurological event is not entered within an expected time frame following cardiac detection. This feature allows the device to begin treating a patient's neurological event before its detection in the brain signal. These termination conditions are defined at block 990 of FIG. 40A and 890 of FIG. 40B.

If the cardiac/respiratory initiated brain therapy has been ongoing for some time, and polling of the brain signal (i.e., processing the brain signal with a neurological event detection algorithm) has indicated the patient is not in a neurological event, then the following may be true:

1. Cardiac/respiratory triggered therapy was successful in aborting the neurological event, and therefore, the neurological event is not detectable in the brain signal.

2. The cardiac/respiratory event was not associated with a neurological event.

In either case, it would be appropriate to change (adjust or terminate) cardiac/respiratory initiated therapy directed specifically at aborting a neurological event. FIG. 57A is a flow chart illustrating the processing steps executed by a processor (e.g., CPU 732 or any other processor). At block 1000 the processor monitors the cardiac or respiratory signals. At block 1002, the processor detects a cardiac or respiratory event in the cardiac or respiratory signals. Based upon a cardiac or respiratory event detection at block 1002, the processor activates the therapy module to provide therapy to the brain at block 1004. The brain signal is monitored at block 1006. This may be a continuation of monitoring of the brain that was already ongoing or it may be initiation of brain monitoring. Once the therapy has been initiated from a cardiac or respiratory detection, the therapy may be changed at block 1008 based on the monitoring of the brain signal.

One embodiment of the process of FIG. 57A is illustrated in FIG. 57B. The processor receives the cardiac or respiratory signals at block 1050. A cardiac or respiratory event is detected at block 1052. The therapy module is activated at block 1054 to provide therapy -to the brain based on a cardiac or respiratory detection. Once therapy has been initiated from a cardiac/respiratory detection, the device monitors the amount of time therapy has been delivered at block 1056. This time period is programmable. The processor continues to receive a brain signal at block 1058. At decision block 1060 the processor determines when the programmed time period has been exceeded without detection of a neurological event in the brain signal. If the answer is “Yes” (i.e., the cardiac or respiratory initiated brain therapy has been ongoing for the programmed time period without the occurrence of a neurological event in the brain signal), then therapy to the brain is discontinued at block 1062. If the patient has entered a neurological event while receiving cardiac/respiratory initiated therapy, control of therapy is transferred to the monitoring of the brain by the neurological event detection algorithm, and therapy decisions are made using the brain signals at block 1064. At this point therapy may continue until the EEG detection algorithm determines that the neurological event has ended. Then therapy may be terminated based on the detected end of the neurological event based on the EEG detection algorithm output.

FIG. 40A discussed above shows a process 971 for determining whether to enable the cardiac or respiratory detectors for neurological event detection and treatment. Once the cardiac or respiratory signals have been enabled for neurological event detection monitoring and treatment at block 986 and the neurological event detection algorithm has been enabled for modulation or other input into cardiac or respiratory therapy, the cardiac/respiratory parameters for stimulation/post-stimulation treatment options are defined at block 987. At block 988, cardiac/respiratory events to treat when in a neurological state are defined. At block 989, cardiac/respiratory events to treat when outside a neurological event are defined. At block 990, therapy termination conditions (i.e., turn over control of brain therapy to the neurological event detection algorithm and terminate if a neurological event is not entered in a programmable period of time) are defined and the monitor starts monitoring or treatment at block 985.

If the matching test of the flow diagram of FIG. 40A shows that one type of cardiac event (type 1) is associated with neurological event onset while other types of cardiac events (type 2) occur frequently, but have no temporal relationship to the neurological event, then the physician may chose to direct therapy to the Brain (or Brain and Heart) upon type 1 event detection or direct therapy to the Heart on type 2 detection.

In the present invention as described in relation to the devices shown above in FIGS. 11-25 and 41-55, the physician is able to selectively choose which cardiac and respiratory events to treat in seizure and non-seizure states. For example, the device may be programmed to treat incidences of tachycardia in non-seizure states, but not in seizure states, where this type of cardiac behavior is expected and considered normal. Also, the patient may experience certain ECG or respiratory abnormalities, which are seizure induced, but cause no complications or increased health risk to the patient. In such cases, the physician may decide to suppress treatment for these events if detected during a seizure. This cannot be accomplished with existing pacemaker technology, which operates on ECG signals only.

There are other instances in which a detected ECG or respiratory abnormality does pose a health risk, regardless of when it occurs and how it was induced. For these events, the physician may choose a mode of operation that treats the ECG/respiratory abnormality in both seizure and non-seizure states (i.e., asystole, apnea).

Additionally, the physician may choose to treat the same ECG/respiratory event in both seizure and non-seizure states, but may define different thresholds (i.e., duration or intensity) for treating the event. For example, during a seizure state, a higher heart rate or sustained occurrence of tachycardia may be required before cardiac treatment is initiated, relative to a non-seizure state. This feature would enable cardiac therapy during status epilepticus, which is a prolonged condition, but suppress it for typical seizure behaviors.

If the matching test of the flow diagram of FIG. 57 shows that the ECG or respiratory signals do not improve seizure detection, but patient is at cardiac risk, the physician may choose to enable the ECG/respiratory detector to deliver therapy to the heart or diaphragm.

If the matching test of the flow diagram of FIG. 57 shows that the ECG or respiratory signals improves seizure detection, but the patient is also at cardiac risk, the physician may choose to treat the brain (for seizures) with EEG, ECG or respiratory detection, and heart (for cardiac problems) with ECG detection.

Preventative Pacing Therapy

Optionally, the therapy systems of FIGS. 11-25 and 41-55 may also have pre-emptive or preventative pacing capabilities. For example, upon EEG detection of seizure onset or imminent seizure onset, the pacing systems described in conjunction with FIGS. 11-25 and 41-55 may begin preventative overdrive pacing to prevent or mitigate sleep apnea such as described in U.S. Pat. No. 6,126,611 “Apparatus for Management of Sleep Apnea” to Bourgeois. The '611 patent detects sleep apnea and begins to pace the heart at a rate of 70-100 PPM (overdrive pacing the sleep intrinsic rate of typically 30-55 BPM) causing arousal and elimination/prevention of sleep apnea. The herein described invention uses the detection of the onset or impending onset of a seizure to trigger sleep apnea overdrive pacing to preemptively prevent the initiation of apnea. Upon the sensing of seizure termination or a preprogrammed timeout, the sleep apnea prevention overdrive pacing is terminated/inactivated.

Alternatively, the pacing systems may begin ventricular pacing overdrive upon sensing a ventricular premature contraction to prevent the initiation of ventricular arrhythmias such as described in U.S. Pat. No. 4,503,857 “Programmable Cardiac Pacemaker with Microprocessor Control of Pacer Rate” to Boute, et al and U.S. Pat. No. 5,312,451 “Apparatus and Methods for Controlling a Cardiac Pacemaker in the Event of a Ventricular Extrasystole” to Limousin, et al: Upon detection of the onset or impending onset of a seizure ventricular extrasystole overdrive pacing may be initiated, and subsequent to the programmed number of cycles, a slowing of the ventricular rate until either the programmed base rate is reached or a sinus detection occurs. Upon the sensing of seizure termination or a preprogrammed timeout, the sleep apnea prevention overdrive pacing is terminated/inactivated.

Additionally, the pacing systems described in conjunction with FIGS. 11-25 and 41-55 may include AF preventative pacing therapies as described in U.S. Pat. No. 6,185,459 “Method and Apparatus for Prevention of Atrial Tachyarrhythmias” to Mehra, et al or U.S. Pat. No. 6,650,938 Method and System for Preventing Atrial Fibrillation by Rapid Pacing Intervention” to Boute. The '459 and '938 patents describe systems that sense premature atrial events and initiate overdrive pacing algorithms to prevent the initiation of atrial arrhythmias. In the present invention, upon detection of the onset or impending onset of a seizure, ventricular extrasystole AF overdrive pacing may be initiated, and subsequent to the programmed number of cycles, a slowing of the ventricular rate until either the programmed base rate is reached or a sinus detection occurs. Upon the sensing of seizure termination or a preprogrammed timeout, the sleep apnea prevention overdrive pacing is terminated/inactivated.

Signal Processing

The signal processing of cardiac, respiration or electroencephalogram signals of the above-described embodiments may include analog, continuous wave bandpass filtering as is well known in the art. Additionally, digital signal processing techniques as substantially described in U.S. Pat. No. 6,029,087 “Cardiac Pacing System with Improved Physiological Event Classification Based Upon DSP” to Wohlgemuth and U.S. Pat. No. 6,556,859 “System and Method for Classifying Sensed Atrial Events in a Cardiac Pacing System” to Wohlgemuth, et al may be used. Additionally, fuzzy logic processing techniques as described in U.S. Pat. No. 5,626,622 “Dual Sensor Rate Responsive Pacemaker” to Cooper and U.S. Pat. No. 5,836,988 “Rate Responsive Pacemaker with Exercise Recovery Using Minute Volume Determination” to Cooper, et al. may be used to determine/detect the occurrence or onset of seizures, respiratory or cardiac anomalies.

The devices of the above-described systems that contain 2 individual units in 2-way communication (e.g., the systems of FIGS. 20-23) may optionally transmit events via the communication channel by one of several ways including, but not limited to, individual event logic signal, marker channel or processed signal.

Power Saving and Clock Synchronization

The devices of the above-described systems that contain 2 individual units in 2-way communication (e.g., the systems of FIGS. 20-23, 43, 45-47, 49, 52, 53, 55) may optionally have a reduced power capability during communication. The devices may communicate at a predefined specific time interval with clocks in each unit of the system updated/resynchronized on each communication (as described in U.S. Pat. No. 6,083,248 “World Wide Patient Location and Data Telemetry System for Implantable Medical Devices” to Thompson. Optionally, a receiving unit may open a window at a period interval (e.g., 1 second) for a brief window (e.g., 100 mSec) to look for an incoming transmission from the other system unit.

Drug Pump

The therapy device in above devices as described in systems as described in conjunction with FIGS. 11-25 and 41-55 may optionally contain a drug pump to deliver liquid medicants in lieu of stimulation or in combination with stimulation. Medicants used could include epileptic drugs (examples of such drugs include, but are not limited to intrathecal delivery of CGX-1007 or Baclofen), mental health and mood disorder related drugs, cardiac drugs (examples of such drugs include, but are not limited to, pharmaceutical compositions comprising beta-adrenergic blocking agents, protain emide, type 1 antiarrhythmic agents such as disopyramide, class II agents such as propafenone, alphaagonists such as ephedrine and midodrine, and other antiarrhymic agents such as amiodarone, and combinations thereof) or respiratory drugs (examples of such drugs include, but are not limited to diuretics).

Remote Monitoring

The present invention also allows the residential, hospital or ambulatory monitoring of at-risk patients and their implanted medical devices at any time and anywhere in the world (see system 900 FIG. 58). Medical support staff 906 at a remote medical support center 914 may interrogate and read telemetry from the implanted medical device and reprogram its operation while the patient 10 is at very remote or even unknown locations anywhere in the world. Two-way voice communications 910 via satellite 904, cellular via link 32 or land lines 956 with the patient 10 and data/programming communications with the implanted medical device 958 via a belt worn transponder 960 may be initiated by the patient 10 or the medical support staff 906. The location of the patient 10 and the implanted medical device 958 may be determined via GPS 902 and link 908 and communicated to the medical support network in an emergency. Emergency response teams can be dispatched to the determined patient location with the necessary information to prepare for treatment and provide support after arrival on the scene. See for example, U.S. Pat. No. 5,752,976 “World Wide Patient Location and Data Telemetry System for Implantable Medical Devices” to Duffin et al.

An alternative or addition to the remote monitoring system as described above in conjunction with FIG. 58 is shown in the system 950 of FIG. 59, which shows a patient 10 sleeping with an implantable Monitor 958 or optional therapy device as described above in connection with the systems of FIGS. 1-57. The implantable device 958, upon detection of a neurological event (such as a seizure), respiratory apnea or cardiac conduction anomaly (ie, heart rate variability, QT extension, arrhythmia) may alert a remote monitoring location via local remote box 952 (as described in U.S. Pat. No. 5,752,976 “World Wide Patient Location and Data Telemetry System for Implantable Medical Devices” to Duffin, et al.) telephone 954 and phone lines 956 or the patient's care provider via an RF link 32 to a pager-sized remote monitor 960 placed in other locations in the house or carried (ie, belt worn) by the care provider 962. The remote caregiver monitor 960 may include audible buzzes/tones/beeps, vocal, light or vibration to alert the caregiver 962 of patient's monitor in an alarm/alert condition. The RF link may include RF portable phone frequencies, power line RF links, HomeRF, Bluetooth, ZigBee, WIFI, MICS band (medical implant communications service), or any other interconnect methods as appropriate. Often the care provider 962 may be able to take some action to help the patient 10. For example, the care provider may arouse the patient 10 from a neurological event (such as a SUDEP episode) by shaking them, arousing them, reposition the patient, or the like.

Patient Alert

The monitor (and optionally therapy) devices as described in systems described above in conjunction with FIGS. 1-57 may optionally allow a patient alert to allow the patient an early warning of impending seizure, respiratory or cardiac anomalies via vibration (e.g., piezo buzzer in implanted device, a vibrator as used in a cell phone or pager in a “silent ring” mode in vest, patch or patient activator), audible buzzing or tones (e.g., audible in cranial implant, audible via external patch, patient activator or vest), light (e.g., external vest or patient activator) or vocal (e.g., spoken word in cranial, vest, external patch, or patient activator) indicators of the monitor in an alarm/alert condition.

It will be apparent from the foregoing that while particular embodiments of the invention have been illustrated and described, various modifications can be made without departing from the spirit and scope of the invention. Accordingly, it is not intended that the invention be limited, except as by the appended claims. 

1. A medical device system comprising: (a) a brain stimulating element for stimulating the brain and outputting a brain stimulation signal; (b) a cardiac monitoring element for sensing activity of the heart and outputting a cardiac signal; and (c) one or more processors in communication with the brain stimulating element and the cardiac monitoring element, the one or more processors configured to: (i) receive the brain stimulation signal; (ii) determine at least one reference point for a stimulation event time period by evaluation of the brain stimulation signal; (iii) receive the cardiac signal; and (iv) identify a first portion of the cardiac signal based on the at least one reference point of the stimulation event time period.
 2. The medical device system of claim 1 wherein the reference point is the starting point of the stimulation event time period and the first portion comprises a pre-event portion.
 3. The medical device system of claim 1 wherein the reference point is the ending point of the stimulation event time period and the first portion comprises a post-event portion.
 4. The medical device system of claim 1 wherein determining the at least one reference point comprises determining a starting point of the stimulation event time period and an ending point of the stimulation event time period, and wherein the first portion of the cardiac signal comprises an event portion of the cardiac signal that is identified based on the starting point and the ending point of the stimulation event time period.
 5. The medical device system of claim 1 wherein the one or more processors are further configured to identify a second portion of the cardiac signal based on the at least one reference point.
 6. The medical device system of claim 4 wherein the one or more processors are further configured to: (a) identify a pre-event portion of the cardiac signal based on the starting point of the stimulation event time period; and (b) identify a post-event portion of the cardiac signal based on the ending point of the stimulation event time period.
 7. The medical device system of claim 4 wherein the event portion of the cardiac signal comprises the cardiac signal from the starting point to the ending point.
 8. The medical device system of claim 4 wherein the evaluation of the brain stimulation signal comprises executing an algorithm, and wherein the brain stimulation event time period is a stimulation period.
 9. The medical device system of claim 2 wherein the pre-event portion of the cardiac signal comprises at least a portion of the cardiac signal before the starting point.
 10. The medical device system of claim 9, wherein the pre-event portion of the cardiac signal comprises the cardiac signal from a first period of time before the starting point to the starting point.
 11. The medical device system of claim 10 wherein the pre-event portion comprises the cardiac signal from the first period of time before the starting point to a second period of time before the starting point.
 12. The medical device system of claim 11 wherein the first period of time and the second period of time are programmable.
 13. The medical device system of claim 3 wherein the post-event portion of the cardiac signal comprises at least a portion of the cardiac signal after the ending point.
 14. The medical device system of claim 3 wherein the post-event portion of the cardiac signal comprises the cardiac signal from the ending point of the stimulation event time period to a third period of time after the ending point.
 15. The medical device of claim 13 wherein the third period of time is programmable.
 16. The medical device system of claim 1 further comprising a memory and wherein the one or more processors are further configured to store the first portion of the cardiac signal in the memory.
 17. The medical device system of claim 5 wherein the one or more processors are further configured to determine a first metric of the first portion of the cardiac signal, and the one or more processors are further configured to determine a second metric of the second portion of the cardiac signal.
 18. The medical device system of claim 17 wherein the one or more processors are further configured to: (a) determine a second metric time related to the amount of time from the at least one reference point to the occurrence of the second portion; (b) determine whether the second metric meets a predetermined criteria about its relationship to the first metric; and (c) record in memory the second metric time when the second metric meets the predetermined criteria.
 19. The medical device system of claim 18 wherein the predetermined criteria are met when the second metric equals the first metric.
 20. The medical device system of claim 18 wherein the predetermined criteria are met when the second metric is within a specified range of the first metric.
 21. The medical device system of claim 18 wherein the first portion comprises a pre-event portion and the second portion comprises a post-event portion, and wherein the first and second metrics comprise heart rate.
 22. The medical device system of claim 17 wherein the one or more processors are further configured to compare the first metric to the second metric.
 23. The medical device system of claim 22 wherein the one or more processors are configured to compare the first metric to the second metric by computing the percentage change from the first metric to the second metric.
 24. The medical device system of claim.22 wherein the cardiac signal includes information about a heart rate, and wherein the first metric is a metric relating to the heart rate during the first portion of the cardiac signal and the second metric is a metric relating to the heart rate during the second portion of the cardiac signal.
 25. The medical device system of claim 24 wherein the first metric is the mean heart rate over the first portion of the cardiac signal, and wherein the second metric is the mean heart rate over the second portion of the cardiac signal.
 26. The medical device system of claim 24 wherein the first metric is the maximum heart rate over the first portion of the cardiac signal, and wherein the second metric is the maximum heart rate over the second portion of the cardiac signal.
 27. The medical device system of claim 24 wherein the first metric is the standard deviation of the heart rate over the first portion of the cardiac signal, and wherein the second metric is the standard deviation of the heart rate over the second portion of the cardiac signal.
 28. The medical device system of claim 24 wherein the first metric is the minimum heart rate over the first portion of the cardiac signal, and wherein the second metric is the minimum heart rate over the second portion of the cardiac signal.
 29. The medical device system of claim 24 wherein the first metric is the median heart rate over the first portion of the cardiac signal, and wherein the second metric is the median heart rate over the second portion of the cardiac signal.
 30. The medical device system of claim 22 wherein the at least one reference point comprises a starting point and an ending point of a stimulation event time period, and wherein the first portion of the cardiac signal comprises a pre-event portion of the cardiac signal based on the starting point of the stimulation event time period, and wherein the second portion of the cardiac signal comprises a post-event portion of the cardiac signal based on the ending point of the stimulation event time period.
 31. The medical device system of claim 22 wherein the at least one reference point comprises a starting point and an ending point of a stimulation event time period, and wherein the first portion of the cardiac signal comprises a pre-event portion of the cardiac signal based on the starting point of the stimulation event time period, and wherein the second portion of the cardiac signal comprises an event portion of the cardiac signal based on the starting and ending points of the stimulation event time period.
 32. The medical device system of claim 22 wherein the at least one reference point comprises a starting point and an ending point of a stimulation event time period, and wherein the first portion of the cardiac signal comprises an event portion of the cardiac signal based on the starting point and the ending point of the stimulation event time period, and wherein the second portion of the cardiac signal comprises a post-event portion of the cardiac signal based on the ending point of the stimulation event time period.
 33. The medical device system of claim 32 wherein the post-event portion of the cardiac signal comprises the cardiac signal from the ending point of the brain event time period to a specified period of time after the ending point of the stimulation event time period.
 34. The medical device system of claim 33 wherein the specified period of time is programmable.
 35. The medical device system of claim 4 wherein the one or more processors determine the ending point of the stimulation event time period by evaluation of the brain stimulation signal.
 36. The medical device system of claim 4 wherein the one or more processors determine the ending point of the stimulation event time period based on the starting point of the stimulation event time period.
 37. The medical device system of claim 1 wherein the brain stimulating element, cardiac monitoring element and one or more processors are configured for implantation in a human body.
 38. The medical device system of claim 18 wherein the system comprises an implantable unit comprising the brain stimulating element, the cardiac monitoring element and at least one implantable processor of the one or more processors, wherein the implantable processor is contained in a hermetically sealed housing for implantation in a human body, and wherein the system further comprises an external device, wherein the external device comprises a second processor of the one or more processors, and wherein the implantable unit comprises a telemetry transmitter, and wherein the external device includes a telemetry receiver for receiving information from the telemetry transmitter.
 39. The medical device system of claim 38 wherein identifying the first portion of the cardiac signal and identifying the second portion of the cardiac signal are performed by the first implantable processor, and wherein determining the first and second metrics and comparing the first and second metrics is performed by the second processor.
 40. The medical device system of claim 38 wherein identifying the first portion of the cardiac signal and identifying the second portion of the cardiac signal and determining the first and second metrics are performed by the first implantable processor, and wherein comparing the first and second metrics is performed by the second processor.
 41. A medical device system comprising: (a) a brain stimulating element for sensing activity of the brain and outputting. a brain signal; (b) a cardiac monitoring element for sensing activity of the heart and outputting a cardiac signal; and (c) one or more processors in communication with the brain stimulating element and the cardiac monitoring element, the one or more processors configured to: (i) receive the brain stimulation signal; (ii) determine at least one reference point of a seizure event time period by evaluation of the brain stimulation signal; (iii) receive the cardiac signal; (iv) identify a first portion of the cardiac signal based on the at least one reference point, the first portion selected from the group consisting of pre-stimulation, stimulation and post-stimulation portions; (v) identify a second portion of the cardiac signal based on the at least one reference point, the second portion different from the first portion and selected from the group consisting of pre-stimulation, stimulation and post-stimulation portions; (vi) determine a first metric of the first portion; (vii) determine a second metric of the second portion; and (viii) compare the first metric to the second metric.
 42. A method of stimulating brain and monitoring cardiac activity comprising: (a) stimulating the brain and outputting a brain stimulation signal; (b) monitoring the heart and outputting a cardiac signal indicative of activity in the heart; (c) determining at least one reference point for a brain stimulation event time period by evaluation of the brain stimulation signal; and (d) identifying a first portion of the cardiac signal based on the at least one reference point of the brain stimulation event time period.
 43. The method of claim 42 wherein the reference point is the starting point of the brain stimulation event time period and the first portion comprises a pre-event portion.
 44. The method of claim 42 wherein the reference point is the ending point of the brain stimulation event time period and the first portion comprises a post-event portion.
 45. The method of claim 42 wherein determining the at least one reference point comprises determining a starting point of the brain stimulation event time period and an ending point of the brain stimulation event time period, and wherein the first portion of the cardiac signal comprises an event portion of the cardiac signal that is identified based on the starting point and the ending point of the brain stimulation event time period.
 46. The method of claim 42 further comprising identifying a second portion of the cardiac signal based on one of the at least one reference point.
 47. The method of claim 43 wherein the pre-event portion of the cardiac signal comprises at least a portion of the cardiac signal before the starting point.
 48. The method of claim 47 wherein the pre-event portion comprises at least a portion of the cardiac signal before a period of time before the starting point.
 49. The method of claim 42 further comprising storing the first portion of the cardiac signal in a memory.
 50. The method of claim 46 further comprising determining a first metric of the first portion of the cardiac signal, and determining a second metric of the second portion of the cardiac signal.
 51. The method of claim 50 further comprising comparing the first metric to the second metric.
 52. The method of claim 51 wherein comparing the first metric to the second metric comprises computing the percentage change from the first metric to the second metric.
 53. The method of claim 51 wherein the cardiac signal includes information about a heart rate, and wherein the first metric is a metric relating to the heart rate during the first portion of the cardiac signal and the second metric is a metric relating to the heart rate during the second portion of the cardiac signal.
 54. The method of claim 53 wherein the first metric is the mean heart rate over the first portion of the cardiac signal, and wherein the second metric is the mean heart rate over the second portion of the cardiac signal.
 55. The method of claim 53 wherein the first metric is the maximum heart rate over the first portion of the cardiac signal, and wherein the second metric is the maximum heart rate over the second portion of the cardiac signal.
 56. The method of claim 53 wherein the first metric is the standard deviation of the heart rate over the first portion of the cardiac signal, and wherein the second metric is the standard deviation of the heart rate over the second portion of the cardiac signal.
 57. The method of claim 53 wherein the first metric is the minimum of the heart rate over the first portion of the cardiac signal, and wherein the second metric is the minimum of the heart rate over the second portion of the cardiac signal.
 58. The method of claim 53 wherein the first metric is the median heart rate over the first portion of the cardiac signal, and wherein the second metric is the median heart rate over the second portion of the cardiac signal.
 59. The method of claim 53 wherein the at least one reference point comprises a starting point and an ending point of a brain stimulation event time period, and wherein the first portion of the cardiac signal comprises a pre-event portion of the cardiac signal based on the starting point of the brain stimulation event time period, and wherein the second portion of the cardiac signal comprises a post-event portion of the cardiac signal based on the ending point of the brain stimulation event time period.
 60. The method of claim 53 wherein the at least one reference point comprises a starting point and an ending point of a brain stimulation event time period, and wherein the first portion of the cardiac signal comprises a pre-event portion of the cardiac signal based on the starting point of the brain stimulation event time period, and wherein the second portion of the cardiac signal comprises an event portion of the cardiac signal based on the starting and ending points of the brain stimulation event time period.
 61. The method of claim 53 wherein the at least one reference point comprises a starting point and an ending point of a brain stimulation event time period, and wherein the first portion of the cardiac signal comprises an event portion of the cardiac signal based on the starting point and the ending point of the brain stimulation event time period, and wherein the second portion of the cardiac signal comprises a post-event portion of the cardiac signal based on the ending point of the brain stimulation event time period.
 62. A computer readable medium containing executable instructions causing a processor to perform the following: (a) receiving a brain stimulation signal from a brain stimulating element; (b) receiving a cardiac signal from a cardiac monitoring element; and (c) determining at least one reference point for a brain stimulation event time period by evaluation of the brain stimulation signal; and (d) identifying a first portion of the cardiac signal based on the at least one reference point of the brain stimulation event time period.
 63. The computer readable medium of claim 62 wherein the executable instructions further cause the processor to identify a second portion of the cardiac signal based on the at least one reference point.
 64. The computer readable medium of claim 63 wherein the executable instructions further cause the processor to determine a first metric of the first portion of the cardiac signal, and determine a second metric of the second portion of the cardiac signal.
 65. The computer readable medium of claim 64 wherein the executable instructions further cause the processor to compare the first metric to the second metric. 